Multi-array probe structure and intracranial hematoma rapid detection system and method

Abstract

The invention provides a multi-array probe structure, and belongs to the field of biomedical optical detection, the multi-array probe structure comprises a plurality of light sources and a plurality of sensors, the plurality of light sources are uniformly distributed along the circumference by taking one sensor as a circle center, the plurality of sensors are arranged between each light source and the circle center at equal intervals, the plurality of light sources alternately emit light, the light is emitted after being absorbed and scattered, the light is received by a plurality of sensors arranged along the radial direction of the light source, and whether hematoma exists in a detected area is judged according to the change rate of the initial light intensity of each light source relative to the emergent light intensity received by each sensor; the invention further provides an intracranial hematoma rapid detection system and method, a multi-channel light path sensing structure is formed by arranging a plurality of light sources and a plurality of sensors, comprehensive scanning of the whole brain area is achieved, the limitation that only symmetric areas can be detected in the prior art is overcome, and the system and method are particularly suitable for detecting hematoma in the asymmetric areas such as the frontal lobe.

Description

Technical Field

[0001] The present invention relates to the technical field of biomedical optical detection, and particularly to a multi-array probe structure, an intracranial hematoma rapid detection system and method. Background Art

[0002] Traumatic brain injury (TBI) refers to brain injury caused by external forces. It can be caused by a strong impact, blow or shaking of the head or body, or by an object entering the brain. The symptoms and severity of TBI can vary, from mild headache and brief loss of consciousness to severe brain tissue damage and long-term health problems.

[0003] Intracranial hematoma (ICH) is a common and serious complication in traumatic brain injury. It refers to the accumulation of blood in the brain after the brain is hit by an external force, causing blood vessels to rupture. The hematoma may cause increased intracranial pressure, which in turn compresses the brain tissue, leading to severe nerve damage. The occurrence of intracranial hematoma will exacerbate the severity of TBI and increase the mortality and the risk of long-term disability of patients. Since intracranial hematoma can progress rapidly within a short time and cause serious complications, early diagnosis and timely treatment are crucial. Currently, clinically, head CT or MRI scans are usually used to timely detect the presence and depth of the hematoma, so as to determine whether surgical intervention is needed. However, due to reasons such as their large volume and cumbersome operation, these devices cannot be applied to the emergency scene. Near-infrared spectroscopy technology has the advantages of non-invasiveness, rapidity, portability, etc. compared with traditional imaging technologies such as CT and MRI. It is very suitable for emergency environments and mobile medical use. It does not rely on large devices and can be designed as a device that is convenient for doctors or emergency personnel to carry and operate quickly at any time, which is of great significance for the early screening and monitoring of emergency and critically ill patients. The American Infrascanner2000 near-infrared spectroscopy brain hematoma scanner has achieved non-invasive and rapid detection of brain hematomas.

[0004] However, existing methods all utilize the difference in absorption degrees on both sides of the intracranial cavity. For example, the American Infrascanner2000 near-infrared spectroscopy brain hematoma scanner needs to compare the left and right sides of the same region of the brain to determine whether there is a hematoma. This detection method requires simultaneous detection of the symmetric two sides of the brain, and judges whether there is a hematoma in the detected area by comparing the absorption differences between the two sides. This not only increases the detection time, but also limits the detection range. Especially for the frontal lobe area lacking symmetry, it is difficult to perform effective detection. In addition, due to the differences in the anatomy and optical properties of the scalp, skull, etc. in the contralateral region, the measurement results are easily affected, resulting in inaccuracy. Summary of the Invention

[0005] The technical problem to be solved by the present invention is how to solve the problem that existing sensing probes are difficult to detect whether there is a hematoma in an asymmetric area.

[0006] The present invention solves the above technical problem through the following technical solutions: A multi-array probe structure includes a plurality of light sources and a plurality of sensors. The plurality of light sources are evenly distributed along a circumference with one of the sensors as the center. A plurality of sensors are arranged at equal intervals between each light source and the center. The plurality of light sources emit light alternately. The light is absorbed and scattered and then emitted, and is received by a plurality of sensors arranged radially along the light source. According to the change rate of the initial light intensity of each light source relative to the emitted light intensity received by each sensor, it is determined whether there is a hematoma in the detected area.

[0007] The multi-array probe structure of the present invention forms a multi-channel optical path sensing structure by setting a plurality of light sources and a plurality of sensors, realizes a comprehensive scan of the whole brain area, overcomes the limitation of traditional technologies that can only detect symmetric areas, and is particularly suitable for detecting hematomas in asymmetric areas such as the frontal lobe. Detection is carried out by using the difference in the change rate between the initial light intensity and the emitted light intensity. When there is a hematoma in the skull, due to the strong absorption of blood, the change rate of the emitted light intensity compared with the initial light intensity will change significantly. The plurality of light sources emit light alternately. The light is absorbed and scattered and then emitted, and is received by a plurality of sensors arranged radially along the light source. The structure of a single light source cooperating with a plurality of sensors can eliminate the change rate difference brought by different depths and improve the detection accuracy.

[0008] Preferably, the wavelength range of the light source is 700nm - 900nm.

[0009] Preferably, the sensor is a photodiode, a silicon photodiode or a charge-coupled device, and the response peak wavelength of the sensor is between 700nm - 900nm.

[0010] Preferably, there are at least 8 light sources. At least 3 sensors are placed between each light source and the center. The plurality of sensors arranged radially along each light source are placed at equal intervals with a spacing of 1cm, and the spacing between each light source and its adjacent sensor is 1cm.

[0011] The present invention also provides a rapid intracranial hematoma detection system, including the multi-array probe structure described above. The detection system further includes a central processing module, a human-computer interaction module, an information display module and a power supply module. The central processing module is connected to the multi-array probe structure for processing the data received by the sensors. The human-computer interaction module is connected to the central processing module for inputting user data. The information display module is connected to the central processing module for displaying the detection results. The power supply module is respectively connected to the central processing module and the human-computer interaction module for power supply.

[0012] The present invention also provides a method for rapid detection of intracranial hematoma. Based on the multi-array probe structure described above, the method includes: closely attaching the multi-array probe structure to the scalp surface, and multiple light sources alternately emit light and enter the human brain tissue. After being absorbed and scattered by the substances in the brain tissue, the light is emitted and received by a plurality of sensors arranged radially along the light source. Based on the initial light intensity of the light source and the emitted light intensity detected by the sensors, the change rate of the initial light intensity relative to the emitted light intensity detected by each sensor is calculated, and then the average value of the change rates is obtained. Based on the average value of the change rates of the initial light intensity of each light source relative to the emitted light intensity, the coefficient of variation of the average value of the change rates is calculated. If the coefficient of variation is greater than the set threshold, it is determined that there is a hematoma in the detected area; otherwise, there is no hematoma.

[0013] Preferably, the change rate of the initial light intensity relative to the emitted light intensity detected by each sensor is calculated as follows:

[0014]

[0015] where is the change rate of the initial light intensity of the i-th light source relative to the emitted light intensity detected by the n-th sensor, is the initial light intensity of the i-th light source, is the emitted light intensity detected by a plurality of sensors arranged radially along the i-th light source, and n is the number of sensors arranged radially along each light source.

[0016] Preferably, the average value of the change rates of the initial light intensity of each light source relative to the emitted light intensity ΔS i is calculated as follows:

[0017]

[0018] where ΔS i is the average value of the change rates of the initial light intensity of the i-th light source relative to the emitted light intensity.

[0019] Preferably, the coefficient of variation CV of the average value of the change rates is calculated as follows:

[0020]

[0021] where μ is the mean value of the average value of the change rates, S is the standard deviation of the average value of the change rates,

[0022] Preferably, the set threshold is 10%.

[0023] The advantages provided by the present invention are:

[0024] (1) The multi-array probe structure of the present invention forms a multi-channel optical path sensing structure by setting multiple light sources and multiple sensors to achieve a comprehensive scan of the entire brain area, overcoming the limitation that traditional technology can only detect symmetrical areas, and is particularly suitable for detecting hematomas in asymmetrical areas such as the frontal lobe. The difference between the initial light intensity and the rate of change of the emitted light intensity is used for detection. When a hematoma appears in the brain, due to the strong absorption of blood, the rate of change of the emitted light intensity compared to the initial light intensity will change significantly. Multiple light sources emit light alternately, and the light is emitted after absorption and scattering, and is received by multiple sensors arranged along the radial direction of the light source. The structure of a single light source combined with multiple sensors can eliminate the difference in the rate of change caused by different depths and improve the accuracy of detection.

[0025] (2) The rate of change of the initial light intensity relative to the outgoing light intensity detected by each sensor is calculated, and then the average value of the rate of change is obtained. Based on the average value of the rate of change of the initial light intensity of each light source relative to the outgoing light intensity, the coefficient of variation of the average values ​​of the rate of change in different directions is calculated. If the coefficient of variation exceeds the set threshold, it can be determined that a hematoma exists in the detected area. There is no need to rely on the measurement results of the symmetrical areas on both sides, which can effectively shorten the detection time. Only the measurement data of the area to be tested is required, which avoids the errors caused by the differences in the skull structure and scalp absorption in the symmetrical areas, and improves the accuracy of judging whether a hematoma exists. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1 A schematic diagram of a multi-array probe structure provided by an embodiment of the present invention;

[0027] Figure 2 A front view of a multi-array probe structure provided by an embodiment of the present invention;

[0028] Figure 3 A structural block diagram of a rapid intracranial hematoma detection system provided by an embodiment of the present invention;

[0029] Figure 4 A schematic diagram of a model of a multi-array probe structure provided in an embodiment of the present invention. DETAILED DESCRIPTION

[0030] In order to make the purpose, technical solution and advantages of the present invention more clearly understood, the technical solution of the present invention is clearly and completely described below in combination with specific embodiments and with reference to the accompanying drawings. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0031] like Figure 1As shown in the figure, this embodiment provides a multi-array probe structure, which includes a plurality of light sources and a plurality of sensors. The plurality of light sources are evenly distributed along the circumference with one of the sensors as the center, and several sensors are arranged at equal intervals between each light source and the center. The plurality of light sources emit light alternately, and after being absorbed and scattered, the light is emitted and received by the plurality of sensors arranged radially along the light source (including the sensor at the center). According to the change rate of the initial light intensity of each light source relative to the emitted light intensity received by each sensor, it is determined whether there is a hematoma in the detected area.

[0032] There are at least 8 light sources. At least 3 sensors are placed between each light source and the center. The plurality of sensors arranged radially along each light source are placed at equal intervals with a spacing of 1 cm, and the spacing between each light source and its adjacent sensor is 1 cm.

[0033] This embodiment takes 8 light sources and 3 sensors placed between each light source and the center as an example to introduce the multi-array probe structure of the present invention:

[0034] The 8 light sources are respectively Light Source 1, Light Source 2, Light Source 3, Light Source 4, Light Source 5, Light Source 6, Light Source 7, and Light Source 8. One of the sensors is arranged at the center of the multi-array probe structure. With this sensor as the center, the 8 light sources are evenly distributed along the circumferential direction, that is, the angle between the radial directions where adjacent two light sources are located is 45°. Refer to Figure 1 , name the sensor at the center as Sensor 1. Between Light Source 1 and Sensor 1, arrange Sensor 2-1, Sensor 3-1, and Sensor 4-1 at equal intervals. Between Light Source 2 and Sensor 1, arrange Sensor 2-2, Sensor 3-2, and Sensor 4-2 at equal intervals. Between Light Source 3 and Sensor 1, arrange Sensor 2-3, Sensor 3-3, and Sensor 4-3 at equal intervals. Between Light Source 4 and Sensor 1, arrange Sensor 2-4, Sensor 3-4, and Sensor 4-4 at equal intervals. Between Light Source 5 and Sensor 1, arrange Sensor 2-5, Sensor 3-5, and Sensor 4-5 at equal intervals. Between Light Source 6 and Sensor 1, arrange Sensor 2-6, Sensor 3-6, and Sensor 4-6 at equal intervals. Between Light Source 7 and Sensor 1, arrange Sensor 2-7, Sensor 3-7, and Sensor 4-7 at equal intervals. Between Light Source 8 and Sensor 1, arrange Sensor 2-8, Sensor 3-8, and Sensor 4-8 at equal intervals. According to the penetration depth of light in the human brain tissue, determine that the spacing between adjacent sensors in the plurality of sensors arranged radially along each light source is 1 cm, and the spacing between each light source and its adjacent sensor is 1 cm. Refer to Figure 2, the distances between Sensor 1 and Sensors 2-7, between Sensors 2-7 and 3-7, between Sensors 3-7 and 4-7, and between Sensor 4-7 and Light Source 7 are all L = 1 cm. The spacing between adjacent sensors in the radial direction of each other light source is set in the same way as that of Light Source 7, which will not be elaborated here.

[0035] To further facilitate the understanding of the distribution of the multi-array probe structure of the present invention, taking the position of Sensor 1 as the origin, the line connecting Light Source 2, Sensor 1, and Light Source 7 as the horizontal direction, and the line connecting Light Source 1, Sensor 1, and Light Source 5 as the vertical direction, the position of any light source or sensor is defined as (x, y, d), where x represents the angle between any light source or sensor and the positive Y-axis, y represents the angle between any light source or sensor and the positive X-axis, and d represents the distance between any light source or sensor and Sensor 1. Thus, Sensor 1 can be represented as (0°, 0°, 0), Sensor 2-1 as (0°, 90°, 1 cm), Sensor 2-8 as (45°, 45°, 1 cm), Sensor 2-7 as (90°, 0°, 1 cm), Sensor 2-6 as (135°, 45°, 1 cm), Sensor 2-5 as (180°, 90°, 1 cm), Sensor 2-4 as (135°, 135°, 1 cm), Sensor 2-3 as (90°, 180°, 1 cm), and Sensor 2-2 as (45°, 135°, 1 cm).

[0036] Sensor 3-1 is represented as (0°, 90°, 2 cm), Sensor 3-8 as (45°, 45°, 2 cm), Sensor 3-7 as (90°, 0°, 2 cm), Sensor 3-6 as (135°, 45°, 2 cm), Sensor 3-5 as (180°, 90°, 2 cm), Sensor 3-4 as (135°, 135°, 2 cm), Sensor 3-3 as (90°, 180°, 2 cm), and Sensor 3-2 as (45°, 135°, 2 cm).

[0037] Sensor 4-1 is represented as (0°, 90°, 3 cm), Sensor 4-8 as (45°, 45°, 3 cm), Sensor 4-7 as (90°, 0°, 3 cm), Sensor 4-6 as (135°, 45°, 3 cm), Sensor 4-5 as (180°, 90°, 3 cm), Sensor 4-4 as (135°, 135°, 3 cm), Sensor 4-3 as (90°, 180°, 3 cm), and Sensor 4-2 as (45°, 135°, 3 cm).

[0038] At this time, the distances between the light source 1 and the sensors 4-1, 3-1, 2-1, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively. The distances between the light source 2 and the sensors 4-2, 3-2, 2-2, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively. The distances between the light source 3 and the sensors 4-3, 3-3, 2-3, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively. The distances between the light source 4 and the sensors 4-4, 3-4, 2-4, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively. The distances between the light source 5 and the sensors 4-5, 3-5, 2-5, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively. The distances between the light source 6 and the sensors 4-6, 3-6, 2-6, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively. The distances between the light source 7 and the sensors 4-7, 3-7, 2-7, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively. The distances between the light source 8 and the sensors 4-8, 3-8, 2-8, and 1 are 1 cm, 2 cm, 3 cm, and 4 cm respectively.

[0039] The light source is composed of laser diodes or light-emitting diodes that can emit single or multiple wavelengths, and the wavelength range of the light source is between 700 - 900 nm to ensure good penetration of the light source into the human brain tissue. The sensor is a photodiode, a silicon photodiode, or a charge-coupled device, and the peak response wavelength of the sensor is between 700 - 900 nm.

[0040] As Figure 3 shown, the present invention also provides an intracranial hematoma rapid detection system, including the above multi-array probe structure. The detection system further includes a central processing module, a human-computer interaction module, an information display module, and a power supply module. The central processing module is connected to the multi-array probe structure for processing the data received by the sensors. The human-computer interaction module is connected to the central processing module for inputting user data. The information display module is connected to the central processing module for displaying the detection results. The power supply module is respectively connected to the central processing module and the human-computer interaction module for power supply.

[0041] The present invention also provides a method for rapidly detecting intracranial hematoma based on the above multi-array probe structure. When detecting intracranial hematoma, Figure 4The multi-array probe structure shown is closely attached to the scalp surface. Multiple light sources alternately emit light and enter the human brain tissue. After being absorbed and scattered by the substances in the brain tissue, the light is emitted and received by several sensors arranged radially along the light source. Based on the initial light intensity of the light source and the emitted light intensity detected by the sensors, the change rate of the initial light intensity relative to the emitted light intensity detected by each sensor is calculated, and then the average value of the change rate is obtained. Based on the average value of the change rate of the initial light intensity of each light source relative to the emitted light intensity, the coefficient of variation of the average value of the change rate is calculated. If the coefficient of variation is greater than the set threshold, it is determined that there is a hematoma in the detected area, otherwise there is no hematoma. The set threshold of the present invention is 10%.

[0042] The change rate of the initial light intensity relative to the emitted light intensity detected by each sensor is calculated as follows:

[0043]

[0044] where is the change rate of the initial light intensity of the i-th light source relative to the emitted light intensity detected by the n-th sensor, is the initial light intensity of the i-th light source, is the emitted light intensity detected by several sensors arranged radially along the i-th light source, and n is the number of sensors arranged radially along each light source.

[0045] The average value of the change rate of the initial light intensity of each light source relative to the emitted light intensity ΔS i is calculated as follows:

[0046]

[0047] where ΔS i is the average value of the change rate of the initial light intensity of the i-th light source relative to the emitted light intensity.

[0048] The calculation method of the coefficient of variation CV of the average value of the change rate is:

[0049]

[0050] where μ is the mean value of the average value of the change rate, S is the standard deviation of the average value of the change rate,

[0051] For the sake of easy understanding, the following takes the arrangement of 8 light sources as an example to introduce the rapid intracranial hematoma detection method of the present invention:

[0052] After the multi-array probe structure is closely attached to the scalp surface, the light sources 1, 2, 3, 5, 6, 7, and 8 in the multi-array probe structure emit light alternately in sequence. The emitted light enters the human brain tissue, and after being absorbed and scattered by the substances in the brain tissue, it exits in a "banana shape" and is received by the sensors on the probe.

[0053] The incident initial light intensity of light source 1 is The light intensities detected by sensors 4-1, 3-1, 2-1, and sensor 1 are The incident initial light intensity of light source 2 is The light intensities detected by sensors 4-2, 3-2, 2-2, and sensor 1 are The incident initial light intensity of light source 3 is The light intensities detected by sensors 4-3, 3-3, 2-3, and sensor 1 are The incident initial light intensity of light source 4 is The light intensities detected by sensors 4-4, 3-4, 2-4, and sensor 1 are The incident initial light intensity of light source 5 is The light intensities detected by sensors 4-5, 3-5, 2-5, and sensor 1 are The incident initial light intensity of light source 6 is The light intensities detected by sensors 4-6, 3-6, 2-6, and sensor 1 are The incident initial light intensity of light source 7 is The light intensities detected by sensors 4-7, 3-7, 2-7, and sensor 1 are The incident initial light intensity of light source 8 is The light intensities detected by sensors 4-8, 3-8, 2-8, and sensor 1 are

[0054] The change rate of the initial light intensity of light source 1 relative to the emitted light intensity detected by sensor 4-1 is The change rate of the initial light intensity of light source 1 relative to the emitted light intensity detected by sensor 3-1 is The change rate of the initial light intensity of light source 1 compared to the emitted light intensity detected by sensor 2-1 is The change rate of the initial light intensity of light source 1 compared to the emitted light intensity detected by sensor 1 is And so on, the change rates of the initial light intensity of light source i (i = 1, 2, 3, 4, 5, 6, 7, 8) compared to the emitted light intensities detected by sensors 4-i, 3-i, 2-i, and sensor 1 are respectively

[0055] Furthermore, it is obtained that the average change rate of the initial light intensity of light source 1 with respect to the detected outgoing light intensities by sensors 4-1, 3-1, 2-1, and 1 is

[0056] The average change rate of the initial light intensity of light source 2 with respect to the detected outgoing light intensities by sensors 4-2, 3-2, 2-2, and 1 is

[0057] The average change rate of the initial light intensity of light source 3 with respect to the detected outgoing light intensities by sensors 4-3, 3-3, 2-3, and 1 is

[0058] The average change rate of the initial light intensity of light source 4 with respect to the detected outgoing light intensities by sensors 4-4, 3-4, 2-4, and 1 is

[0059] The average change rate of the initial light intensity of light source 5 with respect to the detected outgoing light intensities by sensors 4-5, 3-5, 2-5, and 1 is

[0060] The average change rate of the initial light intensity of light source 6 with respect to the detected outgoing light intensities by sensors 4-6, 3-6, 2-6, and 1 is

[0061] The average change rate of the initial light intensity of light source 7 with respect to the detected outgoing light intensities by sensors 4-7, 3-7, 2-7, and 1 is

[0062] The average change rate of the initial light intensity of light source 8 with respect to the detected outgoing light intensities by sensors 4-8, 3-8, 2-8, and 1 is

[0063] Calculate the coefficient of variation CV of the average change rate.

[0064]

[0065] where μ is the mean of the average change rate, S is the standard deviation of the average change rate,

[0066] When the coefficient of variation CV > 10%, it can be determined that there is a hematoma in the detected area; otherwise, there is no hematoma.

[0067] The present invention forms a multi-channel optical path sensing structure by setting multiple light sources and multiple sensors, and performs detection by utilizing the difference between the initial light intensity and the change rate of the outgoing light intensity. When a hematoma appears in the skull, due to the strong absorption of blood, the change rate of the outgoing light intensity compared to the initial light intensity will change significantly. To eliminate the change rate difference caused by different depths, the present invention designs a structure with a single light source and multiple groups of sensors. By calculating the change rate of the initial light intensity relative to the outgoing light intensity detected by each sensor, the average change rate is obtained. Based on the average change rate of the initial light intensity of each light source relative to the outgoing light intensity, the coefficient of variation of the average change rate in different orientations is calculated. If the coefficient of variation exceeds the set threshold, it can be determined that there is a hematoma in the detected area, realizing a comprehensive scan of the whole brain area, overcoming the limitation of the traditional technology that can only detect symmetric areas, and is particularly suitable for detecting hematomas in asymmetric areas such as the frontal lobe, without relying on the measurement results of the symmetric areas on both sides, and can effectively shorten the detection time.

[0068] Since existing devices need to measure on both symmetric sides of the brain and judge according to the light absorption difference between the symmetric sides, the assumed premise is that the absorption effects brought by the skull structures and scalp skin colors on both sides are exactly the same, and the change amount is only the light absorption difference caused by a hematoma on one side and no hematoma on the other side. In fact, the anatomical structures of the two symmetric sides of the human skull are not the same and have obvious differences, and the scalp on both sides may also be difficult to make the light absorption on both symmetric sides exactly the same due to various factors, such as obvious uneven color. The present invention only needs the measurement data of the area to be measured, avoiding the errors caused by the skull structure and scalp absorption differences in the symmetric areas, and improving the accuracy of judging the existence of a hematoma.

[0069] The above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it; although the present invention has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that: they can still modify the technical solutions recorded in the foregoing embodiments, or perform equivalent replacements on some of the technical features; and these modifications or replacements do not make the essence of the corresponding technical solutions deviate from the spirit and scope of the technical solutions of the various embodiments of the present invention.

Claims

1. A multi-array probe structure, characterized in that: The invention comprises a plurality of light sources and a plurality of sensors. The plurality of light sources are evenly distributed along the circumference with one of the sensors as the center. A plurality of sensors are arranged at equal intervals between each light source and the center. The plurality of light sources emit light alternately. The light is emitted after being absorbed and scattered and is received by a plurality of sensors arranged radially along the light source. Whether a hematoma exists in the detected area is determined based on the rate of change of the initial light intensity of each light source relative to the emitted light intensity received by each sensor.

2. The multi-array probe structure according to claim 1, characterized in that: The wavelength range of the light source is 700nm-900nm.

3. The multi-array probe structure according to claim 1, characterized in that: The sensor is a photodiode, a silicon photodiode or a charge coupled device, and the response peak wavelength of the sensor is between 700nm and 900nm.

4. The multi-array probe structure according to claim 1, characterized in that: There are at least 8 light sources, at least 3 sensors are placed between each light source and the center of the circle, multiple sensors arranged radially along each light source are placed at equal intervals with a spacing of 1 cm, and the spacing between each light source and its adjacent sensors is 1 cm.

5. A rapid detection system for intracranial hematoma, comprising the multi-array probe structure according to any one of claims 1 to 4, characterized in that: The detection system also includes a central processing module, a human-computer interaction module, an information display module and a power supply module. The central processing module is connected to the multi-array probe structure for processing data received by the sensor, the human-computer interaction module is connected to the central processing module for inputting user data, the information display module is connected to the central processing module for displaying detection results, and the power supply module is respectively connected to the central processing module and the human-computer interaction module for power supply.

6. A method for rapid detection of intracranial hematoma, based on the multi-array probe structure according to any one of claims 1 to 4, characterized in that: The method comprises: placing the multi-array probe structure in close contact with the scalp surface, allowing multiple light sources to emit light alternately and enter the human brain tissue, and then emitting light after being absorbed and scattered by substances in the brain tissue, and then being received by a number of sensors arranged along the radial direction of the light source; based on the initial light intensity of the light source and the outgoing light intensity detected by the sensor, calculating the change rate of the initial light intensity relative to the outgoing light intensity detected by each sensor, and then obtaining the average value of the change rate; based on the average value of the change rate of the initial light intensity of each light source relative to the outgoing light intensity, calculating the coefficient of variation of the average value of the change rate; if the coefficient of variation is greater than a set threshold value, it is determined that a hematoma exists in the detected area, otherwise it does not exist.

7. The method for rapid detection of intracranial hematoma according to claim 6, characterized in that: The rate of change of the initial light intensity relative to the outgoing light intensity detected by each sensor The calculation method is: in, is the rate of change of the initial light intensity of the i-th light source relative to the outgoing light intensity detected by the n-th sensor, is the initial light intensity of the i-th light source, is the outgoing light intensity detected by several sensors arranged along the radial direction of the i-th light source, and n is the number of sensors arranged along the radial direction of each light source.

8. The method for rapid detection of intracranial hematoma according to claim 7, characterized in that: The average value of the change rate of the initial light intensity of each light source relative to the output light intensity ΔS i The calculation method is: Among them, ΔS i is the average value of the rate of change of the initial light intensity of the i-th light source relative to the output light intensity.

9. The method for rapid detection of intracranial hematoma according to claim 8, characterized in that: The coefficient of variation CV of the mean value of the rate of change is calculated as follows: Among them, μ is the mean of the average value of the rate of change, S is the standard deviation of the mean value of the rate of change, 10. The method for rapid detection of intracranial hematoma according to claim 6, characterized in that: The set threshold is 10%.

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