CN111568440A - Wireless wearable detection system and method for brain blood oxygen in multiple brain areas - Google Patents
Wireless wearable detection system and method for brain blood oxygen in multiple brain areas Download PDFInfo
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- 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, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
- A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, 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, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases specially adapted for cerebral tissue
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0004—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by the type of physiological signal transmitted
- A61B5/0006—ECG or EEG signals
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0015—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by features of the telemetry system
- A61B5/002—Monitoring the patient using a local or closed circuit, e.g. in a room or building
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6802—Sensor mounted on worn items
- A61B5/6803—Head-worn items, e.g. helmets, masks, headphones or goggles
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7225—Details of analog processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2576/00—Medical imaging apparatus involving image processing or analysis
- A61B2576/02—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part
- A61B2576/026—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part for the brain
Abstract
The invention discloses a wireless wearable detection system and a method for brain blood oxygen in multiple brain areas, wherein the system comprises a collector and a plurality of probes, the probes are communicated with the collector through cables, and the probes comprise any one or a combination of a plurality of brain area probes in a forehead brain area probe covering the left side and the right side of a brain, an occipital brain area probe covering the left side and the right side of the brain, a parietal brain area probe and a temporal lobe brain area probe; attaching a plurality of probes to the positions of the divided functional brain areas correspondingly; driving and controlling the probe lights emitted by each probe to the corresponding brain area; each probe simultaneously receives emergent detection light of each functional brain area position and collects brain blood oxygen signals of each brain area; and processing the collected cerebral blood oxygen signals of each cerebral area to obtain cerebral blood oxygen collection information of each cerebral area. The invention can cover the cerebral areas of local anterior circulation cerebral infarction and posterior circulation cerebral infarction by simultaneously detecting a plurality of cerebral areas, thereby solving the limitation that only the anterior circulation cerebral infarction can be reflected.
Description
Technical Field
The invention relates to the technical field of cerebral blood oxygen detection, in particular to a wireless wearable detection system and method for cerebral blood oxygen in multiple cerebral regions.
Background
In the face of stroke, known as "first killer of human health", clinical experts have intensively studied treatment programs. According to Acuteische Stroke Algorithm, published by International Institute for Clinical Systems Improvement at 2016, 12 months, for acute ischemic Stroke, the emphasis in initial examination should include oxygen in addition to vital signs. If the oxygen saturation degree of the brain tissue can be detected, the occurrence of the ischemic stroke can be well evaluated.
Ischemic stroke occupies a large proportion of stroke diseases, and has serious lethality and disability rate. The occurrence of ischemia and anoxia of the brain tissue can be accurately reflected through the blood oxygen reduction of the brain tissue, so the cerebral blood oxygen can be used as an important marker for evaluating the occurrence of ischemic stroke. At present, the "golden standard" for clinically detecting the oxygen saturation of cerebral blood at home and abroad is to collect blood samples of intracranial Jugular glomus (Jugular bulb) at irregular intervals by embedding a catheter in the Jugular vein (Jugular catheterization), and then place the blood samples into a blood gas analyzer for detection to obtain the blood oxygen saturation for evaluating the blood oxygen level of intracranial tissues. On one hand, the invasive detection mode has a larger bleeding risk, and because the detection mode is a deep venous cannula, particularly for middle-aged and elderly people, the deep blood vessel is difficult to find, and if the hemostasis is not in place, the internal bleeding can be caused; on the other hand, the invasive blood sampling is adopted for detection, data acquisition can be carried out only at certain time points, the brain oxygen real-time monitoring cannot be carried out as a monitoring means, and the key treatment period of cerebral apoplexy is easily missed.
With the development of scientific technology, light and photoelectric technology have been effectively and widely used in various fields due to the advantages of biological effectiveness. By utilizing Near Infrared Spectroscopy (NIRS), brain function activity can be detected noninvasively according to the absorption characteristic of hemoglobin in a specific waveband, and the possibility of realizing light CT in the future is further explored. This technology has been developed and achieved in japan, the united states, and the uk. This is a significant attempt to apply advanced photovoltaic technology to medical research. Meanwhile, medical instrument companies also use the technology to provide corresponding high-tech medical instruments for operating rooms, neurology and surgery, obstetrics and gynecology, medicine curative effect detection, brain function research, middle-aged and elderly medical science and other aspects.
In the technology of detecting blood oxygen saturation by using near infrared light, because the forehead has no hair, the transmission and reception of infrared light are not affected, so that the two-channel forehead brain blood oxygen detection technology is mainly used at present. Fore-Sight was developed by CASMED, Japan, Inc. NIR500 and INVOS7100, Medtronic, Inc. of Japan, both of which are used to monitor the blood oxygen saturation level of frontal brain tissue by arranging two optode probes at the forehead. The representative condition in China is a near infrared tissue blood oxygen parameter monitor developed by Qinghua university, which is mainly applied to brain oxygen research, tissue blood oxygen monitoring, sports medicine detection and the like. A cerebral blood oxygen monitor, a cerebral blood oxygen head band and the like are developed by a Chinese academy of sciences, and the real-time monitoring of cerebral blood oxygen, tissue blood oxygen, finger pulse blood oxygen and the like can be realized. For the brain blood oxygen detection, the system carries out detection in a mode that a probe is respectively arranged on the left side and the right side of the forehead.
With the popularization of the products, the related technologies are also gradually applied to the first line of clinical practice, so that light is brought to detection in stroke and bedside monitoring, and the blood oxygen detection of the pre-cerebral circulation during the vascular infarction such as the anterior cerebral artery and the like is realized. It is noted that the prior art detects the blood oxygen saturation of brain tissue through forehead, and uses the blood oxygen saturation of frontal lobe brain tissue as a representative index for evaluating the blood oxygen supply of brain tissue. On the one hand, because no hair at the forehead part influences the infrared light receiving and transmitting, the convenience of instrument development is brought, and the technology and the medical equipment are promoted to enter the clinic. On the other hand, the detection limitation is brought, namely the existing equipment can only detect the attack of cerebral apoplexy when cerebral tissue at forehead part is ischemic and anoxic, which inevitably has certain deficiency and can not reflect the ischemic and anoxic state of brain area closely related to human body movement and visual function, such as apical lobe, occipital lobe and the like.
The most authoritative journal of clinical medicine has been counted. Of the cerebral infarcted patients enrolled in the study, 17% were associated with large anterior circulating infarcts, being cortical and subcortical involvement (total anterior circulating infarcts, TACI); 34% are associated with local anterior cortical infarctions (partial anterior circulatory infarctions, PACI); 24% of infarctions were clearly associated with the basilar vertebral artery region (postcirculatory infarct, POCI); 25% of infarctions were restricted to deep perforated arteries (lacunar infarct, LACI). The existing cerebral blood oxygen saturation detection technology and system collect the blood oxygen saturation of the forehead leaf brain tissue corresponding to the forehead part, and can only reflect TACI, namely large anterior circulation infarction. PACI and POCI have not been accurately characterized and discovered in a timely manner.
According to the results of the survey of the world health organization, the stroke is the second leading cause of death of the global population, is second to cardiovascular diseases, the number of people dying from the stroke in the world every year is up to 570 thousands, and the number of death accounts for about 10 percent of the number of the diseases. Is provided with
The stroke of (1) occurs during hospitalization of the patient, of which nearly half belongs to perioperative stroke. The study showed that only
The stroke occurs perioperatively, i.e. tightly around the bed. In addition, almost 90% of the strokes occur in scenes other than a hospital bed, such as family life, work, parties, and the like. In these scenarios, the bedside monitoring device is not applicable for brain blood oxygen detection. In addition to the above detection, in the environment of hospital outpatient service, there are also a lot of patients with severe stroke that need to detect cerebral blood oxygen. These detection scenarios are all needed to be worn by the patient quickly and give the detection results instantly. In a rescue environment with limited space such as an emergency ambulance, the conventional monitoring device connected by wire is also inconvenient to use due to factors such as cable winding. Because stroke is characterized by high morbidity and high disability rate, about one hundred and fifty million new stroke patients in China each year, and 70-80% of stroke patients need to be rehabilitated because the stroke patients cannot live independently due to disabilities. Apoplexy rehabilitation is the most effective method for reducing disability rate proved by evidence-based medicine, and is an indispensable key link in cerebral apoplexy organized management. In the process of recovery from apoplexy, the same is trueThere is a need for a way to assess brain blood oxygenation restoration in real time. But the existing wired monitor is obviously not suitable for the rehabilitation process.
In order to detect and monitor the blood oxygen saturation of brain tissue of a larger part, it is urgently needed to form a rapid blood oxygen saturation monitoring system covering the main brain functional area of the whole brain, namely a tissue blood oxygen detecting system covering a plurality of brain functional areas of the main perceptual cortex.
Disclosure of Invention
The invention aims to solve the problem that the prior art only realizes the collection limitation of the cerebral blood oxygen saturation of corresponding forehead leaves on two sides of the forehead and meets the monitoring requirement of clinic on the brain tissue of the main functional area of the brain.
The invention adopts the following technical scheme:
in one aspect, the invention provides a wearable wireless multi-brain-area brain blood oxygen detection system.
The utility model provides a wireless many brain areas brain blood oxygen wearable detection system, includes collector and the attached probe of brain area with the head waiting to detect, the probe with communicate through the cable between the collector, the probe is including covering the forehead leaf brain area probe on the left and right sides of brain, the probe still is including being used for covering arbitrary brain area probe or the combination of several brain area probes in occipital lobe brain area probe, parietal lobe brain area probe, the temporalis brain area probe on the left and right sides of brain, a plurality of covers different brain areas the probe respectively with the collector passes through the cable and is connected, the probe is used for the transmission and the receipt of light, the collector is used for controlling each the receipts of probe give out light, and handle the brain area blood oxygen signal that each probe gathered, obtains the brain blood oxygen acquisition information of each brain area.
Furthermore, the system is also provided with a remote controller, the collector and the remote controller are respectively provided with a wireless communication module and/or a wired communication module, the remote controller is also provided with a central processing unit II and a user interaction unit, and the user interaction unit is used for inputting user instructions to each probe, transmitting the user instructions to the central processing unit II and performing remote transceiving control on each probe; the blood oxygen information of the brain area of each probe collected by the collector is sent to the remote controller in a wireless or wired mode, the central processing unit II performs data processing and calculation on the received blood oxygen information of each brain area to obtain the brain blood oxygen saturation data of the brain area corresponding to each probe, and the user interaction unit displays the calculation data of the central processing unit II on the brain blood oxygen saturation of each brain area.
The cerebral blood oxygen saturation data displayed by the user interaction unit comprises cerebral oxygen trend lines of all cerebral regions, cerebral oxygen saturation values, cerebral oxygen difference values among the cerebral regions, change values relative to a baseline and areas under the baseline.
The central processing unit II performs data processing and calculation for each received cerebral region blood oxygen information, and includes:
the data sorting module is used for performing data splitting and channel data sorting on the blood oxygen information of each brain area and summarizing the blood oxygen information into data of each probe light receiving point;
the physiological noise filtering algorithm module is used for filtering physiological noise such as heartbeat, respiration, pulse and the like;
the abnormal data processing algorithm module is used for eliminating abnormal data caused by interference, unexpected jump and the like in the data;
and the cerebral blood oxygen saturation calculation algorithm module is used for calculating the cerebral tissue blood oxygen saturation of each brain area.
Each said visit and collector set up in a silica gel cap, there are luminous point and two light receiving points on the said probe, and there are locating points separately at both ends of the said probe, the said locating point forms the joint with the position-clamping point on the said silica gel cap fixedly.
The collector is internally provided with a plurality of groups of photoelectric conversion units, a plurality of groups of transceiving control units, a central processing unit I and an input and display unit, each group of photoelectric conversion units is correspondingly connected with each group of transceiving control units one by one, the photoelectric conversion units are correspondingly connected with the probes one by one, and the central processing unit I is correspondingly connected with each group of transceiving control units and is used for summarizing the data of the receiving points of the probes, carrying out primary data preprocessing and sending the data to the remote controller through a wired communication module or a wireless communication module; the input and display unit is used for displaying the acquisition state, the working state of each probe and the electric quantity condition.
Preferably, the photoelectric conversion device in the photoelectric conversion unit correspondingly connected with the forehead brain region probe is a PIN-type photodiode; the photoelectric conversion devices in the photoelectric conversion units correspondingly connected with the occipital lobe brain area probe, the parietal lobe brain area probe and the temporal lobe brain area probe are avalanche photodiodes.
Further preferably, a temporary storage unit is further disposed in the collector, and is connected to the central processing unit I, and is configured to store data in the central processing unit I.
The central processing unit I is internally provided with a multi-channel light driving module and an emitting light gain adjusting module which respectively receive a light emitting driving signal and an emitting light gain signal input by a user in the remote controller and control each probe to output the instantaneous light intensity of 0.1-50 mW, so that the photoelectric conversion unit outputs an electric signal of 450-550 mV after photoelectric conversion.
And the remote controller sets the light-emitting driving signals of the multi-path light driving module corresponding to each probe according to a time division multiplexing or frequency division multiplexing mode.
The remote controller is also provided with a database connected with the central processing unit II and used for storing blood oxygen data.
The system is also provided with a cloud database, the cloud database and the remote controller realize data communication in a wireless mode and are used for storing blood oxygen data, and the cloud database is connected with the remote terminals in a wireless mode.
In another aspect, the invention provides a wireless wearable detection method for brain blood oxygen in multiple brain areas.
A wearable detection method for wireless brain blood oxygen in multiple brain areas comprises attaching multiple probes to the positions of each divided functional brain area; respectively driving and controlling the probe lights emitted by each probe to the corresponding brain area; each probe simultaneously receives the emergent detection light of each functional brain area position and acquires each brain area blood oxygen signal; and processing the acquired blood oxygen signals of each brain area to obtain the brain blood oxygen acquisition information of each brain area.
Each divided functional brain region is a main functional region of the brain having cognition, movement, hearing and vision.
Furthermore, the method also comprises the step of carrying out remote data processing and calculation on the acquired blood oxygen information of each brain area to obtain and externally display the cerebral blood oxygen saturation value of the brain area corresponding to each probe.
The wireless wearable detection method for cerebral blood oxygen saturation in multiple brain areas according to claim 15, wherein the cerebral blood oxygen saturation value of each brain area is transmitted to a cloud database, and the cerebral blood oxygen saturation value corresponding to each brain area of the patient is downloaded and displayed from the cloud database by using a remote terminal.
The emitted light of the probes in different brain areas is subjected to multi-path gain adjustment processing, the output instantaneous light intensity of each probe is controlled to be 0.1-50 mW, and the output electric signal of the emitted detection light after photoelectric conversion is 450-550 mV.
And setting a light-emitting driving signal for each probe according to a time division multiplexing or frequency division multiplexing mode, and isolating an emergent light path of each brain area.
Acquiring the brain area blood oxygen signals of the hair area through an orthogonal demodulation method: the incident detection light of each probe is subjected to carrier coding of a specific frequency, and after the probe detects the emergent detection light, the probe orthogonally demodulates the frequency to extract an optical signal of the emergent detection light.
The method for processing the collected blood oxygen signals of the brain areas specifically comprises the following steps: abnormal data detection and correction, sliding window filtering and data packet arrangement of the cerebral blood oxygen optical signals, and the cerebral blood oxygen acquisition information of each cerebral area is obtained by performing photoelectric conversion, signal amplification, analog-to-digital conversion, signal arrangement and data packet processing on the cerebral blood oxygen optical signals.
The technical scheme of the invention has the following advantages:
A. the invention can simultaneously detect the cerebral blood oxygen saturation of a plurality of cerebral areas, can cover the cerebral areas with partial front circulation cerebral infarction and back circulation cerebral infarction, and realizes the detection of the blood oxygen signals of eight cerebral areas including the left and right frontal lobes, the top lobes, the temporal lobes and the occipital lobes simultaneously, thereby monitoring the ischemia and hypoxia states of corresponding main functional areas such as advanced cognition, movement, auditory sensation, vision and the like. Certainly, the invention can also realize the detection of the cerebral blood oxygen saturation of more brain areas according to the invention, or can also carry out the acquisition of multi-cerebral blood oxygen information aiming at specific brain areas, thereby improving the spatial resolution and the efficiency of the cerebral blood oxygen acquisition, and solving the limitations that the existing domestic and foreign cerebral blood oxygen saturation technology and products can only realize the acquisition of the cerebral blood oxygen saturation of corresponding forehead leaves at two sides of the forehead and can only reflect the cerebral anterior circulation cerebral infarction.
B. The system provided by the invention realizes the blood oxygen saturation detection of eight brain areas based on the near infrared spectrum technology. The hair has strong absorption effect on red light and infrared light, so that the detected light intensity is in a nanowatt level, and the detected light intensity of each brain area has large difference due to individual difference, uneven thickness of the skull and the like. In order to ensure that the detected light intensity meets the requirements, the central processing unit I is provided with a multi-channel light driving module and a transmitting light gain adjusting module which respectively receive a light-emitting driving signal and a transmitting light gain signal input by a user in a remote controller, can control each probe to output instantaneous light intensity of 0.1-50 mW, and ensures that the output electric signal after final photoelectric conversion is about 500mV, thereby avoiding the problem that the detection accuracy is influenced by factors such as uneven thickness of hairs and skull bones. Meanwhile, in order to ensure that each brain area has no mutual crosstalk of optical signals during detection, the method adopts a time division multiplexing or frequency division multiplexing mode to isolate optical paths, and improves the detection efficiency and accuracy.
C. Because the frontal lobe, the parietal lobe, the temporal lobe and the occipital lobe of the brain are arranged in different areas of the intracranial, and the thickness, the density, the hair density and the like of the skull between the areas are obviously different, in order to ensure that the collected cerebral tissue blood oxygen saturation, the invention designs the collecting modes and the calculation models of the cerebral blood oxygen saturation of different brain areas according to the analysis of the tissue characteristics and the optical characteristics of the head of a crowd. For example, different photoelectric conversion devices are adopted in the forehead and other areas with hair, the light intensity detected by the forehead can reach uW level, and the detection can be met by applying a common photodiode, and in places with hair, the detection is performed by applying a more sensitive avalanche photodiode due to weaker light intensity, so that the acquisition precision is finally ensured.
D. In the invention, the acquisition of the cerebral blood oxygen saturation of eight cerebral areas can be synchronously realized, and after the cerebral blood oxygen saturation of eight cerebral areas is obtained, the calculation of cerebral oxygen difference of the cerebral areas can be carried out through the central processing unit II. For example, the difference between the cerebral oxygen of the left occipital lobe and the right occipital lobe, or the difference between the cerebral oxygen of the left parietal lobe and the left temporal lobe can be calculated. The result of brain area difference can present in real time, makes things convenient for medical personnel to know brain area blood oxygen difference in time, obtains the accurate data of whole brain blood oxygen, more is favorable to medical personnel to the accurate judgement of patient's state of an illness.
Drawings
In order to more clearly illustrate the embodiments of the present invention, the drawings used in the embodiments will be briefly described below, and it is apparent that the drawings in the following description are some embodiments of the present invention, and other drawings can be obtained by those skilled in the art without inventive efforts.
FIG. 1 is a schematic diagram of multi-brain region cerebral blood oxygen collection provided by the present invention;
FIG. 2 is a schematic plan view of a probe provided by the present invention;
FIG. 3 is a top view of the silicone cap provided by the present invention;
FIG. 4 is a schematic diagram of the main functions of the collector provided by the present invention;
FIG. 5 is a functional schematic of a remote controller provided by the present invention;
FIG. 6 is a block diagram of the data processing components of the CPU II provided by the present invention;
FIG. 7 is a flow chart of a method for detecting cerebral blood oxygen in multiple brain regions according to the present invention.
The labels in the figure are as follows:
1-collector
2-probe
21-prefrontal lobe brain area probe
211-Right prefrontal brain area Probe, 212-left prefrontal brain area Probe
22-occipital lobe brain area probe
221-Right occipital lobe brain region Probe, 222-left occipital lobe brain region Probe
23-apical lobe brain region probe
231-right parietal brain region probe, 232-left parietal brain region probe
24-temporalis lobe brain area probe
241-right temporal lobe brain area probe, 242-left temporal lobe brain area probe
3-a remote controller; 4-a silica gel cap; 5-head.
A-a light emitting point; b-a light collecting point; c-anchor point.
Detailed Description
The technical solutions of the present invention will be described clearly and completely with reference to the accompanying drawings, and it should be understood that the described embodiments are some, but not all embodiments of the present invention. All other embodiments, which can be obtained by a person skilled in the art without any inventive step based on the embodiments of the present invention, are within the scope of the present invention.
As shown in fig. 1 and fig. 2, the present invention provides a detecting system for collecting blood oxygen from brain areas, which comprises a collector 1 and a plurality of probes 2, forming a combination mode shown in fig. 1, wherein during detection, each probe is respectively attached to the brain area to be detected. The number of the probes 2 can be less or more, typically eight probes can be adopted, the arrangement can cover eight brain areas of the brain (as shown by dotted line positions in fig. 1), including occipital lobe, parietal lobe, temporal lobe and frontal lobe on the left and right sides of the head 5, a right prefrontal brain area probe 211 and a left prefrontal brain area probe 212 are respectively arranged at the position of the prefrontal brain area 21, a right occipital lobe brain area probe 221 and a left occipital lobe brain area probe 222 are respectively arranged at the position of the occipital lobe brain area, a right parietal lobe brain area probe 231 and a left parietal lobe brain area probe 232 are respectively arranged at the position of the parietal lobe brain area, and a right temporal lobe brain area probe 241 and a left temporal lobe brain area probe 242 are respectively arranged at the position of the temporal lobe brain area. The probes 2 and the collector 1 are communicated through a wired connection. The cable may be an electrical wire or an optical fiber. In the invention, for example, optical fiber communication is adopted, the collector 1 emits light into the coupled optical fiber, the light reaches the light emitting point A of the probe 2 after passing through the optical fiber, and finally enters the head 5 of the patient. Because the incident red light and infrared light have certain penetrating power, the incident red light and infrared light can penetrate through tissues such as scalp, skull, cerebrospinal fluid and the like and finally reach brain tissues. The light reflected from the brain tissue passes through the cerebrospinal fluid, the skull, and the scalp in reverse order and reaches the probe 2. After receiving the light emitted from the scalp, the light receiving point B in the probe 2 receives the light, and finally transmits the emitted light to the photoelectric conversion device (i.e., the photosensor) in the collector 1 through the optical fiber. If the photoelectric conversion device is designed in the probe 2, photoelectric conversion can be completed on the probe, the probe 2 and the collector 1 only need to be connected and communicated through a cable, the collector can control light emitting and light receiving of each probe, collected blood oxygen information of brain areas is processed, and collection of blood oxygen information of a plurality of required brain areas can be simultaneously realized.
After the blood oxygen information of each brain area is acquired by the collector 1, the blood oxygen saturation in each brain area needs to be further calculated, the system is provided with a remote controller 3, as shown in fig. 4 and 5, the collector 1 and the remote controller 3 are respectively provided with a wireless communication module and/or a wired communication module, the remote controller 3 is also provided with a central processing unit II and a user interaction unit, and the user interaction unit is used for inputting user instructions to each probe 2, transmitting the user instructions to the central processing unit II and performing remote receiving and sending control on each probe; the blood oxygen information of the brain area of each probe collected by the collector is sent to the remote controller in a wireless or wired mode, the central processing unit II carries out data processing and calculation on the received blood oxygen information of each brain area to obtain the brain blood oxygen saturation data of the brain area corresponding to each probe, and the user interaction unit displays the calculation data of the central processing unit II on the brain blood oxygen saturation of each brain area. Specifically, the cerebral blood oxygen saturation data displayed by the user interaction unit includes cerebral oxygen trend lines of respective cerebral regions, cerebral oxygen saturation values, cerebral regional cerebral oxygen difference values, variation values from a baseline, and areas under the baseline.
The following calculation modules are arranged in the central processing unit II, as shown in fig. 6:
the data sorting module is used for performing data splitting and channel data sorting on the blood oxygen information of each brain area and summarizing the blood oxygen information into data of each probe light receiving point;
and the physiological noise filtering algorithm module is used for filtering out physiological noise such as heartbeat, respiration, pulse and the like.
The abnormal data processing algorithm module is used for eliminating abnormal data caused by interference, unexpected jump and the like in the data;
and the cerebral blood oxygen saturation calculation algorithm module is used for calculating the cerebral tissue blood oxygen saturation of each brain area.
Since blood oxygen information of a plurality of brain areas needs to be collected, multiple light emitting and receiving processes need to be performed. In order to reduce mutual crosstalk in multiple channels, the multiple lights can be isolated by time division multiplexing or frequency division multiplexing. In addition, the light energy received at the time of collecting light may vary greatly due to uneven distribution of head tissue, such as distribution of hair, thickness of skull, etc. In order to be able to use the acquisition of different optical signals, different light sensitive devices are used at different locations. For example, in the forehead, a common photodiode can be adopted for optical signal acquisition and conversion. In the hair covering area, the hair absorbs light very strongly, so that the detected light signal is very weak, and a high-sensitivity device such as an avalanche photodiode is required to collect the signal. Aiming at the collection of weak light signals, the invention can also adopt an orthogonal demodulation mode, namely, the incident light is subjected to carrier coding with specific frequency, and the frequency is orthogonally demodulated after the emergent light is detected, so that the extraction of the weak light signals is realized.
In order to more accurately detect the brain area covered by the hair, the output light power is further improved, the irradiation to the brain area covered by the hair is enhanced, the gain adjustment is carried out on the emitted light, the instantaneous power of the output light is enhanced, the penetrating power of the light is improved, and finally the light power emitted from the scalp can be improved. The superficial tissues of the head and the hair density are different in different brain regions, so that the multi-path light output gain adjustment cannot be simply set to be consistent. The invention can adopt manual or self-adaptive or combination of the two modes to carry out multipath gain setting. As shown in fig. 4, the central processing unit I of the collector 1 of the present invention is provided with a multi-channel light driving module and an emitted light gain adjusting module, which respectively receive the light emitting driving signal and the emitted light gain signal input by the user in the remote controller, and control each probe to output an instantaneous light intensity of 0.1mW to 50mW, so that the output electric signal after the photoelectric conversion unit performs photoelectric conversion is 450 mV to 550 mV.
As shown in fig. 4, the collector 1 further includes a plurality of sets of photoelectric conversion units, a plurality of sets of transceiving control units, a central processing unit I, and an input and display unit, each set of photoelectric conversion unit is connected to each set of transceiving control unit in a one-to-one correspondence manner, for example, when detecting 8 brain regions, 8 probes are designed, each probe is connected to a set of photoelectric conversion unit and a set of transceiving control unit, 8 sets of photoelectric conversion units are respectively connected to 8 brain region probes in a one-to-one correspondence manner, and the central processing unit I is connected to 8 sets of transceiving control units in a corresponding manner, and is configured to collect light receiving point data of 8 probes, perform preliminary data preprocessing, and send the data to a remote controller through a wired communication module or a wireless communication module. The input and display unit integrated on the collector mainly completes basic function input, for example, the collector realizes the functions of restarting, resetting and the like. The display unit on the collector can display the collecting state, the working state of each probe and the electric quantity condition. The main collector configuration, data processing and display are not completed on the collector, so the input and display units on the collector are simple, for example, the input and display units can be realized through keys and a display screen.
The collector mainly has the functions of multi-path optical drive, multi-path optical receiving and photoelectric conversion, weak signal amplification, analog-to-digital conversion, data preprocessing, data emission, power management and the like in the system. The functions are realized through corresponding hardware units, and all hardware is the prior art and can be purchased from the market.
As shown in fig. 7, in the wearable wireless multi-brain-area brain blood oxygen detection method, a plurality of probes are correspondingly attached to the positions of the divided functional brain areas; respectively driving and controlling the probe lights emitted by each probe to the corresponding brain area; each probe simultaneously receives the emergent detection light of each functional brain area position and acquires brain blood oxygen signals of each brain area; and processing the collected cerebral blood oxygen signals of each cerebral area to obtain cerebral blood oxygen collection information of each cerebral area. The required cerebral blood oxygen collecting information of each cerebral area can be obtained by synchronous detection of each cerebral area, and the cerebral blood oxygen saturation value can be obtained by performing subsequent calculation processing by using the cerebral blood oxygen collecting information. Each functional brain region divided here is a main functional region of the brain having cognition, movement, hearing, and vision.
The invention carries out remote data processing and calculation on the collected cerebral blood oxygen information of each brain area, for example, the collected cerebral blood oxygen information is sent to a remote controller in a wired or wireless transmission mode, and data calculation is carried out through a central processing unit II in the remote controller, so that the cerebral blood oxygen saturation value of each probe corresponding to each brain area is obtained and displayed outwards, and the difference value of the cerebral blood oxygen saturation of each brain area can also be displayed.
In the following, the present invention will be described in detail with reference to fig. 4 by taking the example that the photosensor is integrated in the collector 1:
the probe is mainly responsible for emitting and receiving light, when the collector receives a collecting command of a far-end controller for brain blood oxygen signals of multiple brain areas, the central processing unit I receives instructions of collecting channels, gain design and the like sent by a user, and after the information is processed, the central processing unit I translates the instructions and sends the translated instructions to the transceiving control unit corresponding to each probe. If the number of the probes is 8, the corresponding number is 8. In each transmit-receive control unit, the transmit light control function will implement the transmit function of the optical path, and perform optical power setting, and then perform light emission drive signal setting according to a time division multiplexing or frequency division multiplexing mode. The transceiving control unit outputs a light source driving signal to the photoelectric conversion unit in which a function corresponding to the light source is photoelectric conversion and light signal emission according to the driving signal. After being generated, the optical signal is input to the light-emitting point of the probe through the optical fiber. The light emitting spot re-emits light to the head.
The light emitted from the head is firstly received by the light receiving point of the probe and then is emitted to the photoelectric conversion unit corresponding to the probe through the optical fiber. The photoelectric conversion unit has a photoelectric conversion device corresponding to the collected optical signal, and converts the received optical signal into an electrical signal. Usually, the electrical signal is very weak, so that the photoelectric conversion unit comprises a device for amplifying the weak electrical signal, and the electrical signal can be amplified to a proper amplitude value, so that the next processing is facilitated. After the photoelectric conversion unit processes the signal, the signal is sent to the corresponding transceiving control unit. In the transceiving control unit, the converted electric signal acquired by the probe is subjected to analog-to-digital conversion, primary processing is performed according to requirements during conversion, and then the digital signal is sent to the central processing unit I.
In the central processing unit I, the digital signals of the respective channels will be collected. Since each probe requires two light receiving points, i.e. each probe will have two received light data. In the case of 8 probes, the central processing unit I will sum the data of the 16 light receiving points. The central processing unit I performs preliminary data preprocessing including abnormal data detection and correction, sliding window filtering, data packet arrangement and the like, and after relevant processing is completed, the central processing unit I sends the data packet to the remote controller through a wired or wireless communication module. The wireless communication mode can be realized through any wireless communication, such as WIFI, bluetooth, and the like.
In order to ensure the brain blood oxygen detection in multiple brain areas and the wearable characteristic of the system, the system (comprising a probe and a collector) can be wirelessly connected with a remote terminal. By adopting wireless communication, the battery pack and the power management unit are integrated on the collector, and as shown in fig. 4, the collector is provided with a power interface at the same time. The power management unit can in time detect the battery pack electric quantity, reminds when the battery pack electric quantity is insufficient, and can supply power to equipment and charge the battery pack when being connected with an external power supply.
Compared with a wired communication mode, the wireless communication mode is easily interfered by external electromagnetic signals and is also easily influenced by space obstacles, so that data cannot be transmitted to a remote controller in real time. In order to ensure that data cannot be lost, a temporary storage unit is also integrated in the collector, and temporary data can be stored. The memory can be a digital memory chip such as FLASH, EEPROM and the like, and can also be a memory such as a U disk, SD card and the like.
As shown in fig. 5, when the optical signal is subjected to photoelectric conversion, signal amplification, analog-to-digital conversion, signal arrangement, data packaging, and then transmitted to the remote controller in a wired or wireless communication manner, the remote controller receives the data packet in real time. The main functions of the remote controller that are closely related to the present invention are shown in fig. 5. The remote controller may be any intelligent device with a corresponding communication interface, such as a smart phone, a smart tablet or a computer. After receiving the data packet, the central processing unit II in the remote controller performs data splitting and channel data sorting, and assembles the data of each light receiving point. Then the central processing unit II starts an internal related algorithm module to process the input data, the algorithm module comprises a physiological noise filtering algorithm module, an abnormal data processing algorithm module and a cerebral blood oxygen saturation calculation algorithm module, cerebral blood oxygen saturation data of a brain area corresponding to each probe are obtained after the processing, and the data can be displayed through a touch screen of the user interaction unit. The display mode may be various, such as a cerebral oxygen trend line of each brain region, a cerebral oxygen saturation value, a cerebral oxygen difference value between brain regions, a change value from a baseline, an area under the baseline (relative baseline value multiplied by time), and the like.
The blood oxygen data is displayed and stored in the database continuously. The database is arranged in the remote controller, and can be established at the cloud end and then sent to the remote controller in a wireless mode, so that a plurality of data display terminals can conveniently read and display data from the cloud end database. The cloud database can read and write data of multiple persons simultaneously, so that the function of monitoring the blood oxygen of the wireless brain areas by the multiple persons can be realized.
The remote controller may further be provided with an input interface, and the user instruction may be input through a touch screen, uploading a configuration file, or the like. The information that the user may enter includes, but is not limited to, patient information, probe configuration, gain configuration, data upload mode, display mode, etc. The user interaction unit is also provided with a display interface, and data can be displayed through a touch screen, a display screen and a display interface (VGA, HDMI and the like).
Each function in the remote controller may be run by means of an instruction set, separate software, an applet, etc. These ways may be determined by the capabilities of the remote control. If the intelligent terminal is an intelligent terminal, such as an android mobile phone, the intelligent terminal can be independently developed into an apk program package, and the user can independently perform interaction such as control and display after directly installing the program package. In the case of a touch screen, the manner of user input and display can be more flexible.
As shown in fig. 2 and fig. 3, the probe 2 and the collector 1 are disposed in a silica gel cap 4, the probe 2 is provided with a light emitting point a and two light receiving points B, and two ends of the probe 2 are respectively provided with positioning points C, the positioning points C and the clamping points on the silica gel cap 4 form a clamping fixation, and the fixation of each probe needs to consider the position of each brain area. The probe is required to be as close to the scalp as possible to ensure that the light-emitting point and the light-collecting point can be attached to the scalp. According to the invention, the probes are preferably fixed in the silica gel cap, the probes are fixed in the silica gel cap through positioning points, and finally all the probes are attached to the scalp through the pulling force of the silica gel cap. The probes can also be connected with each other through the elastic cables between the positioning points, so that the probes can be close to the scalp.
The following is a calculation of the cerebral blood oxygen saturation and related values as follows:
when light in the near infrared band is irradiated through the skull, photons are scattered in the cranium along various paths, a part of the light is absorbed by different layers of tissue such as the skull, scalp and brain, respectively, and the rest of the photons are scattered in the brain tissue along a so-called "banana" model. With the aid of suitable optical devices, we can detect the near-infrared light absorbed and scattered by the brain tissue. Analysis of this emitted light spectrum reveals that the main absorption of near infrared light in brain tissue comes from both deoxyhemoglobin and oxygenated hemoglobin. The change in hemoglobin in brain tissue can be explained by the lambert-beer law, which is as follows:
when the near-infrared light source and the detector are kept at a certain distance and fixed, the detector receives photons emitted after passing through brain tissues, cerebrospinal fluid, skull and scalp. Part of the photons are scattered and absorbed in brain tissue, and the attenuation of light between the light source and the detector is described by formula (1), wherein IinIs incident light, IoutIs to detect light, ODλIs the photon density at wavelength λ and can be defined as the attenuation of the light intensity. The attenuation is the absorption A of light of wavelength λλAnd scattering SλAnd (3) superposition.
Due to intracranial oxygenated hemoglobin (HbO)2) And deoxyhemoglobin (Hb) is the main absorbing substance of near-infrared light. Thus, the absorption of light can be defined as:
Aλ＝∑iξiλCiLλ(3)
wherein i represents oxyhemoglobin and deoxyhemoglobin ξiλIs oxygen-containing or oxygen-removingExtinction coefficient, C, of hemoglobin to near-infrared light of specific wavelength λiIs the concentration of oxygenated or deoxygenated hemoglobin, LλIs the length of the diffusion path of light of wavelength lambda in tissue. The optical density OD can be generated by two optical paths by assuming the difference coefficient of the optical path lengths to be a certain value during scatteringλE.g. subtracting the data of two light receiving points in the probe, i.e. s can be cancelled outλThen the difference in optical density can be expressed as:
the effect of scattering can be eliminated. The concentration of oxygenated or deoxygenated hemoglobin is calculated as follows:
because the absorption coefficient matrix E is known, more accurate parameter values can be given according to the difference of the corresponding head tissue characteristics of a plurality of brain areas and the brain area personalized modeling of the head. At the measured Δ ODλThen the column vector can be obtained
Finally, after light with a plurality of wavelengths is incident, the light can be obtained
The column direction amount of (1). Due to the error of the measurement process, the formula (5) may not be obtained by directly inverting the matrix. The approximate solution can be obtained by solving by methods such as a least square method, compressed sensing and the like. Therefore, the detected near infrared light intensity change signal can be converted into brain activity blood oxygen change, namely hemoglobin concentration change. The final cerebral blood oxygen saturation can be obtained by equation (6) as follows:
the formula (6) shows that,the blood oxygen saturation of the brain tissue is oxygenated hemoglobin in the brain tissue
Account for total hemoglobin
The ratio of (a) to (b).
After obtaining the cerebral blood oxygen saturation values of a plurality of cerebral regions, the cerebral blood oxygen saturation values may be compared with each other, and auc (area Under cut) or the like may be calculated.
The deviation of cerebral blood oxygen saturation from baseline is:
BrSO2＝rSO2-BL (7)
BL denotes a baseline of the cerebral blood oxygen saturation, which may be set manually or an average value over a certain period of time.
The amount of difference in cerebral blood oxygen saturation between brain regions is:
The calculation method of AUC value of cerebral blood oxygen saturation is as follows:
wherein j ═ 0 represents BrSO2At the moment of 0, n stands for the time from BrSO2The nth minute from 0.
The brain blood oxygen saturation degree value and the difference value of each brain area can be obtained in the central processing unit II according to the algorithm formulas. The system can completely get rid of the restriction of cables, broaden the application scenes of cerebral blood oxygen detection and play an important role in the cerebral blood oxygen detection of specific clinical tasks.
It should be understood that the above-described embodiments are merely examples for clarity of description and are not intended to limit the scope of the embodiments. Other variations and modifications will be apparent to persons skilled in the art in light of the above description. This list is neither intended to be exhaustive nor exhaustive. And obvious variations or modifications therefrom are within the scope of the invention.
Claims (20)
1. A wireless wearable detection system for brain blood oxygen in multiple brain areas comprises a collector (1) and a probe (2) attached to a brain area to be detected on the head, wherein the probe (2) is communicated with the collector (1) through a cable, the probe (2) comprises a forehead brain area probe (21) covering the left side and the right side of the brain, and the system is characterized in that the probe (2) further comprises an occipital brain area probe (22) covering the left side and the right side of the brain, a parietal brain area probe (23), a temporal lobe brain area probe (24), any one brain area probe or a combination of a plurality of brain area probes, the plurality of probes (2) covering different brain areas are respectively connected with the collector (1) through cables, the probes (2) are used for emitting and receiving light, the collector (1) is used for controlling the light receiving and emitting of each probe (2) and processing the blood oxygen signals of the brain areas collected by each probe (2), obtaining the cerebral blood oxygen acquisition information of each cerebral area.
2. The wearable wireless multicephalic area brain blood oxygen detection system according to claim 1, wherein the system is further provided with a remote controller (3), the collector (1) and the remote controller (3) are respectively provided with a wireless communication module and/or a wired communication module, the remote controller (3) is further provided with a central processing unit II and a user interaction unit, and the user interaction unit is used for inputting a user instruction to each probe (2), transmitting the user instruction to the central processing unit II, and performing remote transceiving control on each probe; the blood oxygen information of the brain area of each probe collected by the collector is sent to the remote controller in a wireless or wired mode, the central processing unit II performs data processing and calculation on the received blood oxygen information of each brain area to obtain the brain blood oxygen saturation data of the brain area corresponding to each probe, and the user interaction unit displays the calculation data of the central processing unit II on the brain blood oxygen saturation of each brain area.
3. The wearable wireless multi-brain-region brain blood oxygen wearable detection system according to claim 2, wherein the brain blood oxygen saturation data displayed by the user interaction unit comprises brain oxygen trend lines, brain oxygen saturation values, brain oxygen difference values between brain regions, variation values from a baseline, and areas under the baseline of the respective brain regions.
4. The wearable wireless multi-brain-area brain blood oxygen detection system according to claim 3, wherein the central processing unit II performs data processing and calculation for each received brain-area blood oxygen information, and comprises:
the data sorting module is used for performing data splitting and channel data sorting on the blood oxygen information of each brain area and summarizing the blood oxygen information into data of each probe light receiving point;
the physiological noise filtering algorithm module is used for filtering physiological noise such as heartbeat, respiration, pulse and the like;
the abnormal data processing algorithm module is used for eliminating abnormal data caused by interference, unexpected jump and the like in the data;
and the cerebral blood oxygen saturation calculation algorithm module is used for calculating the cerebral tissue blood oxygen saturation of each brain area.
5. The wearable wireless multi-brain-area brain blood oxygen detection system according to claim 1, wherein each probe (2) and each collector (1) are arranged in a silica gel cap (4), the probe (2) is provided with a light emitting point (A) and two light receiving points (B), two ends of the probe (2) are respectively provided with a positioning point (C), and the positioning points (C) and clamping points on the silica gel cap (4) form clamping fixation.
6. The wearable wireless multi-brain-area brain blood oxygen detection system according to any one of claims 2-5, wherein a plurality of sets of photoelectric conversion units, a plurality of sets of transceiving control units, a central processing unit I and an input and display unit are arranged in the collector (1), each set of photoelectric conversion unit is connected with each set of transceiving control unit in a one-to-one correspondence manner, the photoelectric conversion units are connected with the probes in a one-to-one correspondence manner, and the central processing unit I is connected with each set of transceiving control unit in a corresponding manner, and is used for summarizing light receiving point data of each probe, performing preliminary data preprocessing, and sending the data to the remote controller through a wired communication module or a wireless communication module; the input and display unit is used for displaying the acquisition state, the working state of each probe and the electric quantity condition.
7. The wearable wireless multi-brain-area brain blood oxygen detection system according to claim 6, wherein the photoelectric conversion device in the photoelectric conversion unit correspondingly connected to the forehead brain area probe (21) is a PIN photodiode; the photoelectric conversion devices in the photoelectric conversion units correspondingly connected with the occipital lobe brain area probe (22), the parietal lobe brain area probe (23) and the temporal lobe brain area probe (24) are avalanche photodiodes.
8. The wearable wireless multicephalic region brain blood oxygen detection system according to claim 7, wherein a temporary storage unit is further disposed in the collector (1), and is connected to the central processing unit I for storing data in the central processing unit I.
9. The wearable wireless multicephalic region brain blood oxygen detection system according to claim 8, wherein the central processing unit I is provided therein with a plurality of light driving modules and an emitted light gain adjusting module, which respectively receive the emitted light driving signal and the emitted light gain signal inputted by the user in the remote controller, and control each of the probes to output an instantaneous light intensity of 0.1mW to 50mW, so that the output electric signal after the photoelectric conversion unit performs photoelectric conversion is 450 mV to 550 mV.
10. The wearable wireless multi-brain-area brain blood oxygen detection system according to claim 9, wherein the remote controller sets the light emitting driving signals for the multiple optical driving modules corresponding to each of the probes according to a time division multiplexing or frequency division multiplexing mode.
11. The wearable wireless multicephalic region brain blood oxygen detection system according to claim 2, wherein a database connected to the central processing unit II is further disposed in the remote controller for storing blood oxygen data.
12. The wireless wearable multi-brain-area brain blood oxygen detection system according to claim 2, wherein a cloud database is further provided in the system, the cloud database and the remote controller are in data communication in a wireless manner and are used for storing blood oxygen data, and the cloud database is wirelessly connected with a plurality of remote terminals.
13. A wearable detection method for wireless brain blood oxygen in multiple brain areas is characterized in that a plurality of probes are correspondingly attached to the positions of all the divided functional brain areas; respectively driving and controlling the probe lights emitted by each probe to the corresponding brain area; each probe simultaneously receives the emergent detection light of each functional brain area position and acquires each brain area blood oxygen signal; and processing the acquired blood oxygen signals of each brain area to obtain the brain blood oxygen acquisition information of each brain area.
14. The wearable wireless multi-brain-area brain blood oxygen detection method according to claim 13, wherein the divided functional brain areas are main functional areas of the brain with cognition, movement, hearing and vision.
15. The wearable wireless multi-brain-area brain blood oxygen wearable detection method according to claim 13, further comprising performing remote data processing and calculation on the collected blood oxygen information of each brain area to obtain and externally display the value of the blood oxygen saturation of the brain area corresponding to each probe.
16. The wireless wearable detection method for cerebral blood oxygen saturation in multiple brain areas according to claim 15, wherein the cerebral blood oxygen saturation value of each brain area is transmitted to a cloud database, and the cerebral blood oxygen saturation value corresponding to each brain area of the patient is downloaded from the cloud database and displayed by a remote terminal.
17. The wearable wireless multi-brain-area brain blood oxygen detection method according to claim 13, wherein the emitted light from the probes in different brain areas is subjected to multi-channel gain adjustment, so that the instantaneous light intensity output by each probe is controlled to be 0.1-50 mW, and the output electrical signal of the emitted detection light after photoelectric conversion is controlled to be 450-550 mV.
18. The wearable wireless multi-brain-area brain blood oxygen detection method according to claim 17, wherein the light emitting driving signal setting is performed on each probe according to a time division multiplexing or frequency division multiplexing mode, so as to isolate the light path of the emergent light of each brain area.
19. The wearable wireless multi-brain-area brain blood oxygen detection method according to claim 13, wherein the brain-area blood oxygen signals of the hair area are acquired by an orthogonal demodulation method: the incident detection light of each probe is subjected to carrier coding of a specific frequency, and after the probe detects the emergent detection light, the frequency is orthogonally demodulated to extract an optical signal of the emergent detection light.
20. The wearable wireless multi-brain-area brain blood oxygen detection method according to claim 13, wherein processing the collected blood oxygen signals of each brain area specifically comprises: abnormal data detection and correction, sliding window filtering and data packet arrangement of the cerebral blood oxygen optical signals, and performing photoelectric conversion, signal amplification, analog-to-digital conversion, signal arrangement and data packet processing on the cerebral blood oxygen optical signals to obtain cerebral blood oxygen acquisition information of each cerebral area.
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| CN112494039B (en) * | 2021-02-07 | 2021-04-20 | 深圳市第二人民医院(深圳市转化医学研究院) | Visual intelligent monitoring system of brain blood oxygen |
| CN112842332A (en) * | 2021-02-07 | 2021-05-28 | 中国人民解放军南部战区总医院 | Noninvasive remote cerebral oxygen saturation monitoring device |
| CN113951833A (en) * | 2021-11-29 | 2022-01-21 | 武汉资联虹康科技股份有限公司 | Channel pluggable portable near-infrared brain function imaging system and method |
| CN114176522A (en) * | 2021-12-09 | 2022-03-15 | 武汉资联虹康科技股份有限公司 | Near-infrared brain function imaging system with flexibly configurable channels |
| CN114403810A (en) * | 2022-01-24 | 2022-04-29 | 武汉资联虹康科技股份有限公司 | Intelligent head-wearing near-infrared brain function imaging system based on Internet of things |
| CN114391815A (en) * | 2022-03-25 | 2022-04-26 | 慧创科仪(北京)科技有限公司 | Method and system for stroke rehabilitation analysis by using near-infrared brain function imaging device |
| CN116269365A (en) * | 2023-01-04 | 2023-06-23 | 中科搏锐（北京）科技有限公司 | Cerebral blood oxygen monitoring probe, head-mounted equipment and cerebral oxygen monitoring system |
| CN116269365B (en) * | 2023-01-04 | 2024-03-12 | 中科搏锐（北京）科技有限公司 | Cerebral blood oxygen monitoring probe, head-mounted equipment and cerebral oxygen monitoring system |
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