An integrated imaging device and method for monitoring blood oxygen saturation and blood flow velocity

Abstract

This disclosure provides an integrated imaging device and method for monitoring blood oxygen saturation and blood flow velocity. The integrated imaging device includes: a first laser, a second laser, a first dichroic mirror, and a coupler, an optical fiber, a collimator, a second dichroic mirror, and a lens group arranged sequentially along the laser beam transmission direction; wherein the collimator is used to form parallel light from the laser beam output by the optical fiber; the second dichroic mirror is configured to transmit the parallel light and reflect scattered light with a third wavelength; the lens group is used to focus the parallel light onto a set position in the monitoring area of ​​the monitored object; and a transparent ultrasonic transducer, a data acquisition card, a ring light source, a camera module, and a host computer. Using this integrated device, blood oxygen saturation and blood flow velocity information of the monitored area of ​​the monitored object can be obtained. After obtaining this multimodal information, further diagnostic assistance can be provided, improving monitoring efficiency.

Description

Technical Field

[0001] This disclosure relates to the field of brain oxygen monitoring technology, and in particular to an integrated imaging device and method for monitoring blood oxygen saturation and blood flow velocity. Background Technology

[0002] Currently, the main methods for monitoring brain oxygen saturation include near-infrared spectroscopy (NIRS). NIRS utilizes near-infrared light to penetrate the scalp, skull, and brain tissue to measure the relative concentrations of oxyhemoglobin (HbO2) and deoxyhemoglobin (Hb). Based on the differences in absorption spectra, the oxygen saturation of local brain tissue is calculated. The advantages of this method are: (1) non-invasiveness, suitable for long-term monitoring; (2) real-time detection of changes in blood oxygen in local brain regions; and (3) high sensitivity to the oxygen supply and consumption status of specific brain regions.

[0003] Functional magnetic resonance imaging (fMRI) detects brain activity by utilizing changes in blood-oxygen-level dependent (BOLD) signals to reflect the oxygenation status of different brain regions. Active brain regions are enriched with oxyhemoglobin due to increased blood flow, and fMRI can capture these changes in oxygen supply.

[0004] However, while near-infrared spectroscopy and functional magnetic resonance imaging can monitor blood oxygen saturation, they cannot simultaneously monitor cerebral blood flow velocity. This necessitates the addition of a separate blood flow velocity monitoring device, increasing monitoring costs and potentially leading to incompatibility between the new device and the existing blood oxygen saturation monitoring device. This inability to perform simultaneous monitoring results in longer monitoring times, reduced efficiency, and inconvenience. Summary of the Invention

[0005] This disclosure provides an integrated imaging device and method for monitoring blood oxygen saturation and blood flow velocity, thereby addressing at least one of the technical problems existing in the prior art.

[0006] According to a first aspect of this disclosure, an integrated imaging device for monitoring blood oxygen saturation and blood flow velocity is provided, comprising: a first laser configured to emit a first wavelength laser.

[0007] The second laser is configured to emit a second wavelength of laser light.

[0008] The first dichroic mirror is configured to transmit one of the two laser beams, the first wavelength laser and the second wavelength laser, and reflect the other of the two laser beams, thereby transmitting the two laser beams to the coupler.

[0009] And, along the laser light path transmission direction, a coupler, an optical fiber, a collimator, a second dichroic mirror, and a lens group are arranged sequentially; wherein, the coupler is used to couple a first wavelength laser and a second wavelength laser to the optical fiber, the collimator is used to form parallel light from the laser output by the optical fiber; the second dichroic mirror is configured to transmit parallel light and reflect scattered light with a third wavelength; the lens group is used to focus the parallel light to a set position in the monitoring area of ​​the monitored object;

[0010] In addition, a transparent ultrasonic transducer is used to detect the ultrasonic waves emitted when a set position of the monitored object is irradiated by parallel light, thereby forming a photoacoustic signal;

[0011] A data acquisition card, electrically connected to a transparent ultrasonic transducer, is used to acquire the photoacoustic signal and transmit the photoacoustic signal to the host computer.

[0012] The ring light source is configured to emit a third wavelength laser and illuminate the monitoring area of ​​the monitored object to form scattered light, which is then reflected by a second dichroic mirror to the camera module.

[0013] The camera module receives and collects information about the scattered light reflected from the second dichroic mirror;

[0014] The host is used to receive and process scattered light information and photoacoustic signals to obtain the blood oxygen saturation and blood flow velocity information of the monitored area of ​​the monitored object.

[0015] In one possible implementation, it further includes a laser control module electrically connected to the first laser, the second laser, and the host computer, wherein the host computer triggers the first laser and the second laser to emit lasers sequentially by controlling the laser control module.

[0016] In one possible embodiment, the first laser is configured to emit a first wavelength laser with a wavelength of 532 nm;

[0017] The second laser is configured to emit a second wavelength laser with a wavelength of 560 nm.

[0018] In one embodiment, the first dichroic mirror is configured to transmit a second wavelength laser with a wavelength of 560 nm and reflect a first wavelength laser with a wavelength of 532 nm.

[0019] In one embodiment, the second dichroic mirror is configured to transmit laser light with a wavelength of 500-600 nm and reflect light with a wavelength of 780 nm.

[0020] In one embodiment, the wavelength of the third wavelength laser is 780 nm.

[0021] In one embodiment, the incident angle between the first dichroic mirror and the first wavelength laser, as well as the incident angle between the first dichroic mirror and the second wavelength laser, are both 45°.

[0022] The incident angles of the second dichroic mirror with the parallel light and the second dichroic mirror with the scattered light are both 45°.

[0023] In one possible implementation, it further includes a support platform for supporting the monitored object;

[0024] A two-dimensional displacement platform on which the support platform is mounted is electrically connected to the host machine. The two-dimensional displacement platform is configured to synchronously drive the support platform to move in the X and Y directions.

[0025] According to a second aspect of this disclosure, an integrated imaging method for monitoring blood oxygen saturation and blood flow velocity is provided, applied to the integrated imaging device, the method comprising:

[0026] (1) Control the first laser and the second laser to emit lasers in sequence;

[0027] (2) Acquire the photoacoustic signal collected by the data acquisition card. The photoacoustic signal is obtained by the ultrasonic wave emitted at the current set position of the monitoring area of ​​the monitoring object when the laser emitted by the first laser and the second laser acts on the current set position of the monitoring object. The ultrasonic wave emitted at this position is detected and processed by the transparent ultrasonic transducer, thereby completing the acquisition of the current set position.

[0028] (3) Control the two-dimensional displacement platform to move the carrier platform synchronously, thereby driving the monitoring object to collect photoacoustic signals at the next set position;

[0029] (4) Repeat steps (2) to (3) to complete the acquisition of photoacoustic signals at all set positions on the monitoring area of ​​the monitored object, thereby obtaining the blood oxygen saturation information in the monitoring area of ​​the monitored object;

[0030] (5) Control the ring light source to emit light and control the support platform to remain stationary. Obtain the scattered light information collected by the camera module when the ring light source illuminates the monitoring area of ​​the monitored object, and process it to obtain the speckle blood flow velocity information of the monitoring area of ​​the monitored object.

[0031] In one possible implementation, in step (2), combined with Blood oxygen saturation SpO2 = [HbO2] / ([HbO2] + [HbR]) is used to obtain the blood oxygen saturation value of the monitored object at the current set location; where ε HbR (λ i )and These are deoxyhemoglobin and oxyhemoglobin at λ. i Absorption coefficient at wavelength, μ a (λ i ) is λ i The intensity of the photoacoustic signal collected when the wavelength laser acts on the current set position of the monitored object, where HbO2 and HbR represent the concentrations of oxyhemoglobin and deoxyhemoglobin, respectively.

[0032] Compared with existing technologies, the advantages of this application are: 1) The integrated device of this application can obtain the blood oxygen saturation and blood flow velocity information of the monitoring area of ​​the monitored object. After obtaining this multimodal information, it can further assist in diagnosis and improve monitoring efficiency. 2) The integrated device of this application can complete the acquisition of blood oxygen saturation and blood flow velocity information of the monitoring area of ​​the monitored object, saving time and cost.

[0033] It should be understood that the description in this section is not intended to identify key or essential features of the embodiments of this disclosure, nor is it intended to limit the scope of this disclosure. Other features of this disclosure will become readily apparent from the following description. Attached Figure Description

[0034] The above and other objects, features, and advantages of this disclosure will become readily apparent from the following detailed description of exemplary embodiments, taken in conjunction with the accompanying drawings. Several embodiments of this disclosure are illustrated in the drawings by way of example and not limitation, in which:

[0035] In the accompanying drawings, the same or corresponding reference numerals indicate the same or corresponding parts.

[0036] Figure 1 A schematic diagram of the structure of an integrated imaging device according to an embodiment of the present disclosure is shown.

[0037] The reference numerals are as follows: 1-Main unit, 2-Laser control module, 3-First laser, 4-Second laser, 5-First dichroic mirror, 6-Coupled, 7-Fiber optic cable, 8-Collimator, 9-Second dichroic mirror, 10-Lens group, 11-Ring light source, 12-Transparent ultrasonic transducer, 13-Supporting platform, 14-Two-dimensional displacement platform, 15-Camera module, 16-Data acquisition card. Detailed Implementation

[0038] To make the objectives, features, and advantages of this disclosure more apparent and understandable, the technical solutions in the embodiments of this disclosure will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this disclosure, and not all of them. All other embodiments obtained by those skilled in the art based on the embodiments of this disclosure without creative effort are within the scope of protection of this disclosure.

[0039] According to one embodiment of this disclosure, the present invention provides an integrated imaging device for monitoring blood oxygen saturation and blood flow velocity.

[0040] like Figure 1 As shown, the integrated imaging device includes: a first laser 3, configured to emit a first wavelength laser;

[0041] The second laser 4 is configured to emit a second wavelength of laser light;

[0042] The first dichroic mirror 5 is configured to transmit one of the two laser beams, the first wavelength laser and the second wavelength laser, and reflect the other of the two laser beams, thereby transmitting the two laser beams to the coupler 6.

[0043] The system includes a coupler 6, an optical fiber 7, a collimator 8, a second dichroic mirror 9, and a lens group 10 arranged sequentially along the laser light path transmission direction. The coupler 6 couples a first-wavelength laser and a second-wavelength laser to the optical fiber 7; the optical fiber 7 transmits the laser to the collimator 8; the collimator 8 forms parallel light from the laser output from the optical fiber 7; the second dichroic mirror 9 is configured to transmit parallel light and reflect scattered light with a third wavelength; and the lens group 10 focuses the parallel light transmitted from the second dichroic mirror to a set position in the monitoring area of ​​the monitored object.

[0044] In addition, a transparent ultrasonic transducer 12 is used to detect the ultrasonic waves emitted when the set position of the monitored object is irradiated by parallel light, form a photoacoustic signal and transmit it to the data acquisition card.

[0045] Data acquisition card 16 is electrically connected to the ultrasonic transducer and is used to acquire the photoacoustic signal output by the transparent ultrasonic transducer and transmit the photoacoustic signal to the host 1.

[0046] The ring light source 11 is configured to emit a third wavelength laser and illuminate the monitoring area of ​​the monitored object with the third wavelength laser, so that the monitoring area of ​​the monitored object forms scattered light, and then the scattered light is reflected to the camera module by the second dichroic mirror.

[0047] Camera module 15 receives and collects information on scattered light reflected from the second dichroic mirror;

[0048] The host 1 is electrically connected to the camera module 15, the ring light source 11, and the data acquisition card 16. The host 1 receives the scattered light information and the photoacoustic signal transmitted by the data acquisition card, processes them, and obtains the blood oxygen saturation and blood flow velocity information of the monitoring area of ​​the monitored object.

[0049] In this embodiment, the device of this application further includes a laser control module 2, which is electrically connected to the first laser 3, the second laser 4 and the host 1. The host 1 triggers the first laser and the second laser to emit lasers in sequence by controlling the laser control module 2.

[0050] In this device, the first laser, the second laser, and the ring light source emit light sequentially, with only one type of light source illuminating the monitored object at any given time. However, the duration of each illumination is very short, and the switching frequency of the switching switch is very high. Therefore, this device can illuminate the same location of the monitored object's monitoring area with two different wavelengths of laser light. The ultrasound emitted from this same location is detected by the transparent ultrasonic transducer 12, thereby obtaining the photoacoustic signals corresponding to the two wavelengths of laser light at the same location, and thus obtaining the blood oxygen saturation at that location. Therefore, using this integrated device, it is possible to obtain the blood oxygen saturation and blood flow velocity information of the monitored area of ​​the monitored object. After obtaining this multimodal information, further diagnostic assistance can be provided, improving monitoring efficiency.

[0051] For example, the first laser 3 is configured to emit a first wavelength laser with a wavelength of 532 nm;

[0052] The second laser 4 is configured to emit a second wavelength laser with a wavelength of 560 nm.

[0053] The first dichroic mirror 5 is configured to transmit a second wavelength laser with a wavelength of 560 nm and reflect a first wavelength laser with a wavelength of 532 nm.

[0054] The second dichroic mirror 9 is configured to transmit laser light with a wavelength of 500-600 nm and reflect light with a wavelength of 780 nm.

[0055] The third wavelength laser has a wavelength of 780nm.

[0056] For example, lens group 10 commonly includes plano-convex lenses, biconvex lenses, and aspherical lenses. Plano-convex lenses have one convex side and one flat side, making them suitable for collimation and focusing applications. The curved surface is often oriented towards the light source for optimal performance. Biconvex lenses have convex surfaces on both sides, making them ideal image relay elements. Aspherical lenses can eliminate spherical aberration and other aberrations, and are often used in laser focusing and other scenarios.

[0057] The function of a lens group is to focus and collimate the laser beam, enabling the laser to effectively illuminate the target object and generate a photoacoustic signal. Combining different types of lenses allows for better control of the optical path and improves image quality.

[0058] In this application, the lens group 10 is used to focus parallel light onto a set position in the monitoring area of ​​the monitored object.

[0059] For example, the incident angle between the first dichroic mirror 5 and the first wavelength laser, as well as the incident angle between the first dichroic mirror and the second wavelength laser, are both 45°.

[0060] The incident angles of the second dichroic mirror 9 with the parallel light and the incident angles of the second dichroic mirror with the scattered light are both 45°.

[0061] For example, the device of this application also includes a support platform 13 for supporting the monitoring object;

[0062] A two-dimensional displacement platform 14, on which a support platform is mounted, is electrically connected to the host unit 1. The two-dimensional displacement platform 14 is configured to synchronously move the support platform in the X and Y directions. For example, the two-dimensional displacement platform includes a first linear module and a second linear module mounted on the output end of the first linear module and synchronously moving linearly along the X direction following the output end. The output end of the second linear module can move linearly along the Y direction, and the support platform is mounted on the output end. Thus, the two-dimensional displacement platform can synchronously move the monitored object on the support platform to complete scanning monitoring.

[0063] In this application, the host 1, laser control module 2, first laser 3, second laser 4, first dichroic mirror 5, coupler 6, optical fiber 7, collimator 8, second dichroic mirror 9, lens group 10, ring light source 11, transparent ultrasonic transducer 12, support platform 13, two-dimensional displacement platform 14, camera module 15, and data acquisition card 16 can all be obtained commercially.

[0064] In this application, the laser control module 2 controls the first laser 3 and the second laser 4 to emit light sequentially. The light emitted by the first laser 3 and the second laser 4 passes through the first dichroic mirror 5, where it is reflected and transmitted, respectively. Then, the laser light is coupled to the optical fiber 7 via the coupler 6. After the laser light exits the optical fiber, it passes through the collimator 8 to form parallel light (the coupler 6 is connected to the collimator 8 via the optical fiber 7). The light then passes through the second dichroic mirror 9 and is focused by the lens group 10 onto a set location within the monitoring area of ​​the monitored object (e.g., a set location on the brain of the monitored object). At this time, the monitored object emits ultrasound based on the laser irradiation, which is detected by the transparent ultrasonic transducer 12, forming a photoacoustic signal. This photoacoustic signal is then transmitted to the data acquisition card 16, and subsequently to the host computer 1.

[0065] The illumination light emitted by the ring light source 11 (780nm) shines on the monitoring area of ​​the monitored object. The illumination light is scattered by the monitoring area and then reflected by the second dichroic mirror 9 to the camera module 15. At this time, the scattered light information of the monitoring area of ​​the monitored object is received and collected by the camera module 15.

[0066] In this application, the monitoring subjects include, but are not limited to, animals and humans, and the monitoring areas include, but are not limited to, brain regions. For animals, this can assist researchers in conducting multi-faceted experiments and improve monitoring efficiency. For human health monitoring, especially for patients with Alzheimer's disease (AD), the brain's oxygen demand becomes even more critical due to the extensive neuronal damage and degeneration in the brains of Alzheimer's patients. If blood oxygen saturation decreases (e.g., due to sleep apnea, lung disease, or cardiovascular problems), the brain may experience hypoxia, further exacerbating cognitive decline. Alzheimer's patients often have other health problems, such as cardiovascular disease and sleep apnea, which can cause fluctuations in blood oxygen saturation. If a patient has these conditions concurrently, low blood oxygen saturation may negatively impact the brain, further aggravating Alzheimer's symptoms. Furthermore, Alzheimer's patients often exhibit reduced overall cerebral blood flow, particularly in key areas such as the hippocampus and frontal lobe. These areas are closely related to memory, cognition, and decision-making abilities. Reduced blood flow may be due to insufficient blood supply caused by arteriosclerosis, capillary atrophy, or other vascular diseases. Studies show that cerebral blood flow velocity is significantly reduced in Alzheimer's patients compared to healthy individuals. This slowed blood flow is particularly noticeable in vessels such as the middle cerebral artery and basilar artery, indicating limited oxygen and nutrient supply to the brain. Monitoring cerebral blood flow velocity in Alzheimer's patients helps assess disease progression and develop treatment plans. Improving cerebral blood flow (e.g., controlling blood pressure, improving cardiovascular health, and promoting vasodilation) may, to some extent, slow disease progression or improve cognitive function in patients.

[0067] Therefore, in view of the current shortcomings of AD diagnosis, such as difficulty in early diagnosis, invasiveness of existing detection methods, poor repeatability, and high examination costs, the integrated device of this application provides a non-invasive, multimodal detection method for AD diagnosis, which can detect the brain oxygen saturation and blood flow velocity of AD patients, providing a feasible solution for AD diagnosis and monitoring.

[0068] The integrated device of this application can obtain blood oxygen saturation and blood flow velocity information of the monitored area of ​​the monitored object, such as blood oxygen saturation and blood flow velocity information of the brain function of the monitored object. After obtaining this multimodal information, it can further assist in diagnosis and improve monitoring efficiency.

[0069] The integrated device of this application can acquire hemoglobin distribution information, blood oxygen saturation information, and blood flow velocity information in a single scan. After acquiring multimodal information, it can further assist in diagnosis.

[0070] According to one embodiment of this disclosure, the present invention also provides an integrated imaging method for measuring brain oxygen saturation and blood flow velocity, applied to the aforementioned integrated imaging device, the method comprising:

[0071] Step (1): Place the object to be monitored on the carrier platform and set the area to be scanned, that is, determine the monitoring area required for the object to be monitored; the laser control module 2 triggers the first laser 3 and the second laser 4 to emit lasers in sequence; specifically, the host 1 controls the laser control module 2 to work, and the laser control module 2 then triggers the first laser 3 and the second laser 4 to emit the first wavelength laser and the second wavelength laser in sequence respectively.

[0072] Step (2): Acquire the photoacoustic signal collected by the data acquisition card 16. The photoacoustic signal is obtained by the ultrasonic wave emitted at the current set position of the monitoring area of ​​the monitoring object when the laser emitted by the first laser and the second laser acts on the monitoring area of ​​the monitoring object. The ultrasonic wave emitted at the current set position is detected and processed by the transparent ultrasonic transducer (12), thereby completing the acquisition of two photoacoustic signals at the current set position. Specifically, the first wavelength laser and the second wavelength laser emitted by the first laser and the second laser pass through the first dichroic mirror 5, and then through the coupler 6, optical fiber 7, and collimator 8 to form parallel light. The second dichroic mirror 9 transmits the parallel light and then illuminates the lens group 10. The lens group 10 focuses the parallel light on the current set position of the monitoring area of ​​the monitoring object. The ultrasonic wave emitted at the current set position is detected by the transparent ultrasonic transducer 12, thereby forming a photoacoustic signal and transmitting the photoacoustic signal to the data acquisition card 16. The data acquisition card 16 transmits the photoacoustic signal to the host 1.

[0073] Step (3): Control the two-dimensional displacement platform 14 to synchronously drive the bearing platform 13 to move, thereby driving the monitored object to collect photoacoustic signals at the next position;

[0074] Step (4) is repeated by repeating steps (2) to (3) to complete the acquisition of photoacoustic signals at all locations in the monitoring area of ​​the monitored object, thereby obtaining the blood oxygen saturation information in the monitoring area of ​​the monitored object;

[0075] Step (5): Control the ring light source 11 to emit light and control the support platform 13 to remain stationary. Obtain the scattered light information collected by the camera module 15 when the ring light source illuminates the monitoring area of ​​the monitored object, and process it to obtain the speckle blood flow velocity information of the monitoring area of ​​the monitored object.

[0076] Therefore, the method of this application mainly utilizes the host 1 to trigger the first laser 3 (532nm), the second laser 4 (560nm), and the ring light source 11 (780nm) to emit light sequentially through the laser control module 2. After the first laser 3 (532nm) emits light, the transparent ultrasonic transducer 12 detects the ultrasound and acquires the signal through the data acquisition card 16; after the second laser 4 (560nm) emits light, the transparent ultrasonic transducer 2 detects the ultrasound and acquires the signal through the data acquisition card 16; after the ring light source 11 (780nm) emits light, the camera module 15 is triggered to continuously acquire the scattered signal multiple times. Thus, the photoacoustic signals excited by 532nm and 560nm, as well as the scattered signals generated by the ring light source (780nm), are all acquired.

[0077] In step (2), based on the two photoacoustic signals, combined with Blood oxygen saturation SpO2 = [HbO2] / ([HbO2] + [HbR]) is used to obtain the blood oxygen saturation value of the monitored object at the current set location; where ε HbR (λ i )and These are deoxyhemoglobin and oxyhemoglobin at λ. i Absorption coefficient at wavelength, μ a (λ i ) is λ i The intensity of the photoacoustic signal collected when the wavelength laser acts on the current set position of the monitored object, where HbO2 and HbR represent the concentrations of oxyhemoglobin and deoxyhemoglobin, respectively.

[0078] In this application, blood oxygen saturation is calculated as follows: SpO2 = [HbO2] / ([HbO2] + [HbR]), where [HbO2] and [HbR] represent the concentrations of oxyhemoglobin and deoxyhemoglobin, respectively. Hemoglobin is the primary absorber in the blood within the visible light spectrum; therefore, at a wavelength of λ... i Blood absorption signal intensity μ a (λ i ) can be represented as: Where ε HbR (λ i )and These are deoxyhemoglobin and oxyhemoglobin at λ. i The absorption coefficient (constant) at a given wavelength. Therefore, by exciting the same location with dual wavelengths of 532 nm and 560 nm, different absorption signal intensities (i.e., the intensity μ of the photoacoustic signal) can be obtained. a (λ iThen, by solving the equation, we can obtain [HbO2] and [HbR], which represent the concentrations of oxygenated hemoglobin and deoxygenated hemoglobin, respectively, and thus obtain the blood oxygen saturation.

[0079] In this application, speckle blood flow velocity information is acquired as follows: When the ring light source 11 (780nm) illuminates the monitoring area of ​​the target, the scattering signal is continuously acquired multiple times by the camera module 15. If red blood cells move within the field of view of the camera module 15, the laser speckle pattern will fluctuate accordingly. The rate of change of the laser speckle pattern depends on the target's movement speed within the monitoring area; the faster the target moves, the more obvious the speckle pattern changes. The spatial and temporal changes in speckle pattern intensity contain velocity information of the moving scattering body. The faster the scattering body moves, the faster the speckle pattern fluctuates, and the more blurred the speckle pattern recorded by the camera during exposure is. The degree of blurring can be quantified by calculating the speckle contrast value K, where K is defined as the ratio of the standard deviation σ of the light intensity to the average light intensity. The ratio: Therefore, by analyzing the light scattering signals from the same location multiple times, the relative blood flow velocity information at all locations in the field of view can be obtained.

[0080] Information about blood flow velocity is indirectly obtained by calculating the contrast of a speckle image (i.e., speckle contrast ratio). The smaller the speckle contrast ratio, the faster the blood flow velocity; conversely, the larger the speckle contrast ratio, the slower the blood flow velocity.

[0081] Commonly used laser speckle contrast analysis methods include laser speckle spatial contrast analysis (LSSCA), laser speckle temporal contrast analysis (LSTCA), and laser speckle spatiotemporal combined analysis (stLASCA). These methods differ in how they select the original speckle data, but they all assess blood flow velocity based on speckle contrast calculations.

[0082] It should be understood that the various forms of processes shown above can be used to rearrange, add, or delete steps. For example, the steps described in this disclosure can be executed in parallel, sequentially, or in different orders, as long as the desired result of the technical solution disclosed in this disclosure can be achieved, and this is not limited herein.

[0083] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one of that feature. In the description of this disclosure, "a plurality of" means two or more, unless otherwise explicitly specified.

[0084] The above description is merely a specific embodiment of this disclosure, but the scope of protection of this disclosure is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this disclosure should be included within the scope of protection of this disclosure. Therefore, the scope of protection of this disclosure should be determined by the scope of the claims.

Claims

1. An integrated imaging device for monitoring blood oxygen saturation and blood flow velocity, characterized in that: include: The first laser (3) is configured to emit a first wavelength laser. The second laser (4) is configured to emit a second wavelength laser. The first dichroic mirror (5) is configured to transmit one of the two laser beams, the first wavelength laser and the second wavelength laser, and reflect the other of the two laser beams, so that the two laser beams are transmitted to the coupler. And, along with a coupler (6), an optical fiber (7), a collimator (8), a second dichroic mirror (9), and a lens group (10) arranged sequentially along the laser light path transmission direction; wherein, the coupler (6) is used to couple the first wavelength laser and the second wavelength laser to the optical fiber, the collimator is used to form parallel light from the laser output by the optical fiber; the second dichroic mirror is configured to transmit parallel light and reflect scattered light with a third wavelength; the lens group is used to focus the parallel light to a set position in the monitoring area of ​​the monitoring object; And a transparent ultrasonic transducer (12) is used to detect the ultrasonic waves emitted when a set position of the monitored object is irradiated by parallel light, thereby forming a photoacoustic signal; The data acquisition card (16) is electrically connected to the transparent ultrasonic transducer and is used to acquire the photoacoustic signal and transmit the photoacoustic signal to the host. The ring light source (11) is configured to emit a third wavelength laser and irradiate the monitoring area of ​​the monitored object to form scattered light, which is then reflected by a second dichroic mirror to the camera module. The camera module (15) receives and collects information on the scattered light reflected from the second dichroic mirror; The host (1) is used to receive and process scattered light information and photoacoustic signals to obtain the blood oxygen saturation and blood flow velocity information of the monitored area of ​​the monitored object.

2. The integrated imaging device according to claim 1, characterized in that: It also includes a laser control module (2), which is electrically connected to the first laser, the second laser and the host, and the host triggers the first laser and the second laser to emit lasers in sequence by controlling the laser control module.

3. The integrated imaging device according to claim 1, characterized in that: The first laser (3) is configured to emit a first wavelength laser with a wavelength of 532 nm; The second laser (4) is configured to emit a second wavelength laser with a wavelength of 560 nm.

4. The integrated imaging device according to claim 3, characterized in that: The first dichroic mirror (5) is configured to transmit a second wavelength laser with a wavelength of 560nm and reflect a first wavelength laser with a wavelength of 532nm.

5. The integrated imaging device according to claim 1, characterized in that: The second dichroic mirror (9) is configured to transmit laser light with a wavelength of 500-600 nm and reflect light with a wavelength of 780 nm.

6. The integrated imaging device according to claim 5, characterized in that: The wavelength of the third wavelength laser is 780nm.

7. The integrated imaging device according to claim 1, characterized in that: The incident angles of the first dichroic mirror and the first wavelength laser, as well as the incident angles of the first dichroic mirror and the second wavelength laser, are both 45°. The incident angles of the second dichroic mirror with the parallel light and the incident angles of the second dichroic mirror with the scattered light are both 45°.

8. The integrated imaging device according to any one of claims 1-7, characterized in that: It also includes a support platform (13) for supporting the monitored object; A two-dimensional displacement platform (14) is provided, on which the bearing platform is installed. The two-dimensional displacement platform is electrically connected to the host and is configured to synchronously drive the bearing platform to move in the X and Y directions.

9. An integrated imaging method for monitoring blood oxygen saturation and blood flow velocity, applied to the integrated imaging device according to any one of claims 1-8, characterized in that: The method includes: (1) Control the first laser (3) and the second laser (4) to emit lasers in sequence; (2) Acquire the photoacoustic signal collected by the data acquisition card (16). The photoacoustic signal is obtained by the transparent ultrasonic transducer (12) when the laser emitted by the first laser and the second laser acts on the current set position of the monitoring area of ​​the monitoring object. This completes the acquisition of the two photoacoustic signals at the current set position. (3) Control the two-dimensional displacement platform (14) to move the carrier platform synchronously, thereby driving the monitoring object to collect the photoacoustic signal at the next set position; (4) Repeat steps (2) to (3) to complete the acquisition of photoacoustic signals at all set positions on the monitoring area of ​​the monitored object, thereby obtaining the blood oxygen saturation information in the monitoring area of ​​the monitored object; (5) Control the ring light source (11) to emit light and control the support platform to remain stationary. Obtain the scattered light information collected by the camera module (15) when the ring light source illuminates the monitoring area of ​​the monitored object, and process it to obtain the speckle blood flow velocity information of the monitoring area of ​​the monitored object.

10. The method according to claim 9, characterized in that: In step (2), the intensity of the photoacoustic signal is combined Blood oxygen saturation SpO2 = [HbO2] / ([HbO2] + [HbR]) yields the blood oxygen saturation value at the current set location of the monitored object; where ε HbR (λ i )and These are deoxyhemoglobin and oxyhemoglobin at λ. i Absorption coefficient at wavelength; μ a (λ i ) is λ i The intensity of the photoacoustic signal collected when the wavelength laser acts on the current set position of the monitored object; HbO2 and HbR represent the concentrations of oxyhemoglobin and deoxyhemoglobin, respectively.

Images