Integrated imaging device and method for monitoring oxyhemoglobin saturation and blood flow velocity

Abstract

The invention provides an integrated imaging device and method for monitoring oxyhemoglobin saturation and blood flow velocity. The integrated imaging device comprises a first laser, a second laser, a first dichroscope, and a coupler, an optical fiber, a collimator, a second dichroscope and a lens group which are sequentially arranged along the transmission direction of a laser light path, wherein the collimator is used for enabling laser output by the optical fiber to form parallel light; the second dichroscope is configured to be capable of transmitting the parallel light and reflecting the scattered light with the third wavelength; the lens group is used for gathering the parallel light to a set position of a monitoring area of a monitoring object; the system further comprises a transparent ultrasonic transducer, a data acquisition card, an annular light source, a camera module and a host. By means of the integrated device, the blood oxygen saturation degree information and the blood flow velocity information of the monitoring area of the monitoring object can be obtained, diagnosis can be further assisted after the multi-mode information is obtained, and the monitoring efficiency is improved.

Description

Technical Field

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

[0002] Currently, the main methods for monitoring brain blood oxygen saturation are near-infrared spectroscopy (NIRS). NIRS uses near-infrared light to penetrate the scalp, skull, and brain tissue to measure the relative concentrations of oxygenated hemoglobin (HbO2) and deoxygenated hemoglobin (Hb). Based on the difference in absorption spectra, the blood oxygen saturation of local brain tissue is calculated. The advantages of this solution are: (1) it is non-invasive and suitable for long-term monitoring, (2) it can detect blood oxygen changes in local brain areas in real time, and (3) it is very sensitive to the oxygen supply and consumption of specific brain areas.

[0003] Functional Magnetic Resonance Imaging (fMRI) uses changes in blood-oxygen-level-dependent (BOLD) signals to reflect the oxygenation status of different brain regions when detecting brain activity. Active brain regions are rich in oxygenated hemoglobin due to increased blood flow, and fMRI can capture this change in oxygen supply.

[0004] However, near-infrared spectroscopy and functional magnetic resonance imaging can monitor blood oxygen saturation, but they cannot monitor the blood flow velocity in the brain at the same time. It is also necessary to install a blood flow velocity monitoring device, which increases the monitoring cost and may also cause the new device to be incompatible with the original blood oxygen saturation monitoring device. The inability to complete simultaneous monitoring will lead to longer monitoring time and reduced monitoring efficiency, which is inconvenient. Summary of the invention

[0005] The present disclosure provides an integrated imaging device and method for monitoring blood oxygen saturation and blood flow velocity, so as to at least solve one of the technical problems existing in the prior art.

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

[0007] A second laser is configured to emit laser light of a second wavelength,

[0008] A first dichroic mirror is configured to transmit one of the first wavelength laser and the second wavelength laser and reflect the other of the two lasers, so that the two lasers are transmitted to the coupler;

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

[0010] and, a transparent ultrasonic transducer for detecting ultrasound 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 the transparent ultrasonic transducer, for acquiring the photoacoustic signal and transmitting the photoacoustic signal to a host;

[0012] an annular light source configured to emit a third wavelength laser and irradiate the third wavelength laser onto a monitoring area of ​​the monitoring object to form scattered light, and the scattered light is then reflected by the second dichroic mirror to the camera module;

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

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

[0015] In one possible implementation, the device further includes a laser control module 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.

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

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

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

[0019] In one possible implementation, 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 possible implementation, the wavelength of the third wavelength laser is 780 nm.

[0021] In one possible implementation, the incident angle between the first dichroic mirror and the first wavelength laser, and the incident angle between the first dichroic mirror and the second wavelength laser are both 45°;

[0022] An incident angle between the second dichroic mirror and the parallel light and an incident angle between the second dichroic mirror and the scattered light are both 45°.

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

[0024] A two-dimensional displacement platform, on which the carrying platform is installed, the two-dimensional displacement platform is electrically connected to the host, and the two-dimensional displacement platform is configured to be able to synchronously drive the carrying platform to move in the X and Y directions.

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

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

[0027] (2) obtaining a photoacoustic signal collected by a data acquisition card, wherein the photoacoustic signal is when the lasers emitted by the first laser and the second laser act on the currently set position of the monitoring area of ​​the monitored object, and the ultrasound emitted at the position is detected and processed by the transparent ultrasonic transducer, thereby completing the collection of the currently set position;

[0028] (3) Controlling the two-dimensional displacement platform to synchronously drive the carrier platform to move, thereby driving the monitored object to collect the photoacoustic signal at the next set position;

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

[0030] (5) Control the annular light source to emit light and control the supporting platform not to move, obtain scattered light information collected by the camera module when the annular light source irradiates the monitoring area of ​​the monitoring object, and process the scattered light information to obtain the speckle blood flow velocity information of the monitoring area of ​​the monitoring object.

[0031] In one embodiment, in step (2), in combination Blood oxygen saturation SpO2 = [HbO2] / ([HbO2] + [HbR], to obtain the blood oxygen saturation value of the current set position of the monitored object; wherein, ε HbR (λ i )and Deoxygenated hemoglobin and oxygenated hemoglobin are i Absorption coefficient at wavelength, μ a (λ i ) is λ i When the wavelength laser acts on the currently set position of the monitored object, the intensity of the collected photoacoustic signal, HbO2 and HbR represent the oxygenated hemoglobin concentration and the deoxygenated hemoglobin concentration respectively.

[0032] Compared with the prior art, the advantages of the present application are: 1) The integrated device of the present application can obtain the blood oxygen saturation information and blood flow velocity information of the monitoring area of ​​the monitored object. After obtaining these multi-modal information, it can further assist diagnosis and improve monitoring efficiency. 2) The integrated device of the present application can complete the blood oxygen saturation information and blood flow velocity information of the monitoring area of ​​the monitored object, saving time and cost.

[0033] It should be understood that the content described in this section is not intended to identify the key or important features of the embodiments of the present disclosure, nor is it intended to limit the scope of the present disclosure. Other features of the present disclosure will become easily understood through the following description. BRIEF DESCRIPTION OF THE DRAWINGS

[0034] The above and other objects, features and advantages of the exemplary embodiments of the present disclosure will become readily understood by reading the detailed description below with reference to the accompanying drawings. In the accompanying drawings, several embodiments of the present disclosure are shown in an exemplary and non-limiting manner, in which:

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

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

[0037] Description of the accompanying drawings: 1-host, 2-laser control module, 3-first laser, 4-second laser, 5-first dichroic mirror, 6-coupler, 7-optical fiber, 8-collimator, 9-second dichroic mirror, 10-lens group, 11-ring light source, 12-transparent ultrasonic transducer, 13-carrying platform, 14-two-dimensional displacement platform, 15-camera module, 16-data acquisition card. DETAILED DESCRIPTION

[0038] In order to make the purpose, features, and advantages of the present disclosure more obvious and easy to understand, the technical solutions in the embodiments of the present disclosure will be clearly and completely described below in conjunction with the drawings in the embodiments of the present disclosure. Obviously, the described embodiments are only part of the embodiments of the present disclosure, not all of the embodiments. Based on the embodiments in the present disclosure, all other embodiments obtained by those skilled in the art without creative work are within the scope of protection of the present disclosure.

[0039] According to one embodiment of the present 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 laser of a first wavelength;

[0041] A second laser 4, configured to emit laser light of a second wavelength;

[0042] The first dichroic mirror 5 is configured to transmit one of the first wavelength laser and the second wavelength laser and reflect the other of the two lasers, so that the two lasers are transmitted to the coupler 6;

[0043] And, a coupler 6, an optical fiber 7, a collimator 8, a second dichroic mirror 9 and a lens group 10 are sequentially arranged along the transmission direction of the laser light path; wherein the coupler 6 is used to couple the first wavelength laser and the second wavelength laser to the optical fiber 7; the optical fiber 7 is used to transmit the laser to the collimator 8; the collimator 8 is used to form parallel light from the laser output from the optical fiber 7; the second dichroic mirror 9 is configured to be able to transmit the parallel light and reflect the scattered light with a third wavelength; the lens group 10 is used to gather the parallel light transmitted from the second dichroic mirror to a set position of the monitoring area of ​​the monitoring object;

[0044] and, a transparent ultrasonic transducer 12 for detecting the ultrasound emitted when the set position of the monitored object is irradiated by parallel light, forming a photoacoustic signal and transmitting it to a data acquisition card;

[0045] A data acquisition card 16, electrically connected to the ultrasonic transducer, for collecting the photoacoustic signal output by the transparent ultrasonic transducer and transmitting the photoacoustic signal to the host 1;

[0046] The annular light source 11 is configured to emit a third wavelength laser and irradiate the third wavelength laser on the monitoring area of ​​the monitoring object, so that the monitoring area of ​​the monitoring object forms scattered light, and then the scattered light is reflected by the second dichroic mirror to the camera module;

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

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

[0049] In this embodiment, the device of the present application also 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 controls the laser control module 2 to trigger the first laser and the second laser to emit lasers in sequence.

[0050] In the device of the present application, the first laser, the second laser and the ring light source all emit light in sequence, and only one light source irradiates the monitored object at a time point, but the irradiation time is very short, and the switching frequency of the switching switch is very fast. Therefore, through the device of the present application, the two wavelength lasers can be irradiated to the same position of the monitoring area of ​​the monitored object respectively, and the ultrasound emitted from the same position is detected by the transparent ultrasonic transducer 12, so as to obtain the photoacoustic signals corresponding to the two wavelength lasers at the same position, and then obtain the blood oxygen saturation at the position. Therefore, the integrated device of the present application can obtain the blood oxygen saturation information and blood flow velocity information of the monitoring area of ​​the monitored object. After obtaining these multi-modal information, it can further assist diagnosis and improve monitoring efficiency.

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

[0052] The second laser 4 is configured to be able to emit second wavelength laser light having a wavelength of 560 nm.

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

[0054] The second dichroic mirror 9 is arranged so as to transmit laser light having a wavelength of 500 to 600 nm and reflect light having a wavelength of 780 nm.

[0055] The wavelength of the third wavelength laser is 780 nm.

[0056] For example, the lens group 10 commonly includes plano-convex lenses, biconvex lenses, aspheric lenses, etc. Plano-convex lenses have one convex side and one flat side, and are suitable for collimation and focusing applications, and the curved surface is often facing the light source to obtain the best performance; biconvex lenses have both convex sides and are ideal image relay elements; aspheric lenses can eliminate spherical aberration and other aberrations, and are often used in scenes such as laser focusing.

[0057] Function of lens group: used to focus and collimate the laser beam, so that the laser can effectively irradiate the target object and generate photoacoustic signals. The combination of different types of lenses can better control the light path and improve the imaging quality.

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

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

[0060] The incident angle between the second dichroic mirror 9 and the parallel light and the incident angle between the second dichroic mirror and the scattered light are both 45°.

[0061] For example, the device of the present application further includes a carrying platform 13 for carrying the monitored object;

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

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

[0064] In the present application, the laser control module 2 controls the first laser 3 and the second laser 4 to emit light in sequence, and the light emitted by the first laser 3 and the second laser 4 passes through the first dichroic mirror 5, and is reflected and transmitted by the first dichroic mirror 5 respectively, and then the laser is coupled to the optical fiber 7 through the coupler 6. After the laser is transmitted out of the optical fiber, it passes through the collimator 8 to form parallel light (the coupler 6 is connected to the collimator 8 through the optical fiber 7), and then through the second dichroic mirror 9 and then through the lens group 10 to the set position inside the monitoring area of ​​the monitoring object (for example, it is gathered to a set position of the brain of the monitoring object). At this time, the monitoring object will emit ultrasound based on the irradiation of the laser, which is detected by the transparent ultrasonic transducer 12 to form a photoacoustic signal, and the photoacoustic signal is transmitted to the data acquisition card 16, and then transmitted to the host 1.

[0065] The illumination light emitted by the ring light source 11 (780nm) is irradiated onto the monitoring area of ​​the monitored object. The illumination light is scattered by the monitoring area and then reflected to the camera module 15 through the second dichroic mirror 9. 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 objects include but are not limited to animals and humans, and the monitoring areas include but are not limited to brain areas. For animals, it can assist researchers in conducting multi-faceted experiments to improve monitoring efficiency. For human health monitoring, especially Alzheimer's disease (AD) patients, there are a lot of neuronal damage and degeneration in the brains of Alzheimer's patients, which makes the brain's demand for oxygen more critical. If the blood oxygen saturation decreases (such as due to apnea, lung disease or cardiovascular problems), the brain may be hypoxic, further exacerbating the decline of cognitive function. Alzheimer's patients are often accompanied by other health problems, such as cardiovascular disease, sleep apnea, etc., which can cause blood oxygen saturation fluctuations. If the patient suffers from these diseases at the same time, low blood oxygen saturation may have a negative impact on the brain, further exacerbating the symptoms of Alzheimer's disease. In addition, Alzheimer's patients often show a decrease in overall brain blood flow, especially in certain key areas such as the hippocampus and frontal lobe. These areas are closely related to memory, cognition and decision-making ability. The reduction in blood flow may be due to insufficient blood supply caused by vascular hardening, capillary atrophy or other vascular diseases. Studies have shown that the cerebral blood flow rate in patients with Alzheimer's disease is significantly lower than that in healthy individuals. In particular, in blood vessels such as the middle cerebral artery and the basilar artery, a slowdown in blood flow can be found, indicating that the brain's oxygen and nutrient supply is limited. Monitoring the cerebral blood flow rate in patients with Alzheimer's disease helps to assess the progression of the disease and develop a treatment plan. Improving cerebral blood flow (such as controlling blood pressure, improving cardiovascular health, and promoting vasodilation) may slow down the progression of the disease or improve the patient's cognitive function to a certain extent.

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

[0068] By using the integrated device of the present application, it is possible to obtain the blood oxygen saturation information and blood flow velocity information of the monitored area of ​​the monitored object, such as the blood oxygen saturation information and blood flow velocity information of the brain function of the monitored object. After obtaining these multimodal information, it can further assist diagnosis and improve monitoring efficiency.

[0069] The integrated device of the present application can obtain hemoglobin distribution information, blood oxygen saturation information, and blood flow velocity information after a single scan. After obtaining multi-modal information, it can further assist in diagnosis.

[0070] According to an embodiment of the present disclosure, the present invention further provides an integrated imaging method for brain blood oxygen saturation and blood flow velocity, which is applied to the above-mentioned integrated imaging device, and the method includes:

[0071] Step (1), placing the monitored object on the carrier, setting the area to be scanned, that is, determining the monitoring area required by the monitored object; 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 further 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), obtaining the photoacoustic signal collected by the data acquisition card 16, wherein the photoacoustic signal is when the lasers emitted by the first laser and the second laser act on the currently set position of the monitoring area of ​​the monitoring object, the ultrasound emitted at the position is detected and processed by the transparent ultrasonic transducer (12), thereby completing the collection of the two photoacoustic signals at the currently 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 respectively, and then pass through the coupler 6, the optical fiber 7, and the collimator 8 to form parallel light, the second dichroic mirror 9 transmits the parallel light, and then irradiates the lens group 10, the lens group 10 focuses the parallel light on the currently set position of the monitoring area of ​​the monitoring object, the ultrasound emitted at the currently set position is detected by the transparent ultrasonic transducer 12, and then forms a photoacoustic signal and transmits the photoacoustic signal to the data acquisition card 16, and the data acquisition card 16 transmits the photoacoustic signal to the host 1;

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

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

[0075] Step (5) controls the annular light source 11 to emit light, and controls the supporting platform 13 not to move, obtains scattered light information collected by the camera module 15 when the annular light source irradiates the monitoring area of ​​the monitoring object, and processes the scattered light information to obtain the speckle blood flow velocity information of the monitoring area of ​​the monitoring object.

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

[0077] Wherein, in step (2), based on the two photoacoustic signals, combined with Blood oxygen saturation SpO2 = [HbO2] / ([HbO2] + [HbR], to obtain the blood oxygen saturation value of the current set position of the monitored object; wherein, ε HbR (λ i )and Deoxygenated hemoglobin and oxygenated hemoglobin are i Absorption coefficient at wavelength, μ a (λ i ) is λ i When the wavelength laser acts on the currently set position of the monitored object, the intensity of the photoacoustic signal collected, HbO2 and HbR represent the oxygenated hemoglobin concentration and the deoxygenated hemoglobin concentration respectively.

[0078] In this application, the calculation of blood oxygen saturation: The definition of blood oxygen saturation is as follows: SpO2 = [HbO2] / ([HbO2] + [HbR]), where [HbO2] and [HbR] represent the concentration of oxygenated hemoglobin and deoxygenated hemoglobin, respectively. Hemoglobin is the main absorber in the blood within the visible light spectrum, so at a wavelength of λ i The absorption signal intensity μ of blood a (λ i ) can be expressed as: where ε HbR (λ i )and are deoxygenated hemoglobin and oxygenated hemoglobin in λ i Therefore, by exciting the same position with dual wavelengths of 532nm and 560nm, different absorption signal intensities (i.e., the intensity μ of the photoacoustic signal) can be obtained. a (λ i)), and then we can solve the equation to get [HbO2] and [HbR], which represent the concentration of oxygenated hemoglobin and deoxygenated hemoglobin, respectively, and then we can get the blood oxygen saturation.

[0079] In the present application, speckle blood flow velocity information is obtained: when the annular light source 11 (780nm) irradiates the monitoring area of ​​the monitored object, the scattered signal is collected multiple times continuously through the camera module 15. If the red blood cells move in the field of view of the camera module 15, the laser speckle pattern will fluctuate accordingly. The speed of change of the laser speckle pattern depends on the moving speed of the target in the monitoring area; the faster the target moves, the more obvious the change in the speckle pattern. The spatial and temporal changes in the intensity of the speckle pattern contain the velocity information of the moving scatterer. The faster the scatterer moves, the faster the speckle pattern fluctuates, and the blurrier the speckle pattern recorded by the camera during exposure. The degree of blur can be quantified by calculating the speckle contrast ratio value K, which is defined as the standard deviation σ of the light intensity and the average light intensity. Ratio of: Therefore, by analyzing the light scattering signals at the same position multiple times, the relative blood flow velocity information at all positions in the field of view can be obtained.

[0080] The information of blood flow velocity is indirectly obtained by calculating the contrast of the 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 the selection of original speckle data, but all are based on the calculation of speckle contrast to evaluate blood flow velocity.

[0082] It should be understood that the various forms of processes shown above can be used to reorder, add or delete steps. For example, the steps recorded in this disclosure can be executed in parallel, sequentially or in different orders, as long as the desired results of the technical solutions disclosed in this disclosure can be achieved, and this document does not limit this.

[0083] In addition, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include at least one of the features. In the description of the present disclosure, "plurality" means two or more, unless otherwise clearly and specifically defined.

[0084] The above is only a specific embodiment of the present disclosure, but the protection scope of the present disclosure is not limited thereto. Any person skilled in the art who is familiar with the technical field can easily think of changes or substitutions within the technical scope disclosed in the present disclosure, which should be included in the protection scope of the present disclosure. Therefore, the protection scope of the present disclosure should be based on the protection scope of the claims.

Claims

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

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 the second wavelength laser light having a wavelength of 560 nm and reflect the first wavelength laser light having a wavelength of 532 nm.

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 to 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 angle between the first dichroic mirror and the first wavelength laser, and the incident angle between the first dichroic mirror and the second wavelength laser are both 45°; An incident angle between the second dichroic mirror and the parallel light and an incident angle between the second dichroic mirror and the scattered light are both 45°.

8. The integrated imaging device according to any one of claims 1 to 7, characterized in that: It also includes a carrying platform (13) for carrying the monitored object; A two-dimensional displacement platform (14) is provided with the support platform, the two-dimensional displacement platform is electrically connected to the host, and the two-dimensional displacement platform is configured to synchronously drive the support 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 to 8, characterized in that: The method comprises: (1), controlling the first laser (3) and the second laser (4) to emit lasers in sequence; (2) obtaining a photoacoustic signal collected by a data acquisition card (16), wherein the photoacoustic signal is the ultrasound emitted by the transparent ultrasonic transducer (12) when the lasers emitted by the first laser and the second laser act on the currently set position of the monitoring area of ​​the monitoring object, thereby completing the collection of the two photoacoustic signals at the currently set position; (3) controlling the two-dimensional displacement platform (14) to synchronously drive the carrier to move, thereby driving the monitored object to collect the photoacoustic signal at the next set position; (4) Repeating steps (2) to (3) to complete the acquisition of photoacoustic signals at all set positions on the monitoring area of ​​the monitoring object, thereby obtaining blood oxygen saturation information in the monitoring area of ​​the monitoring object; (5) controlling the annular light source (11) to emit light and controlling the supporting platform not to move, obtaining scattered light information collected by the camera module (15) when the annular light source irradiates the monitoring area of ​​the monitoring object, and processing the scattered light information to obtain the speckle blood flow velocity information of the monitoring area of ​​the monitoring object.

10. The method according to claim 9, characterized in that: In the step (2), the intensity of the photoacoustic signal is combined Blood oxygen saturation SpO2 = [HbO2] / ([HbO2] + [HbR], to obtain the blood oxygen saturation value of the current set position of the monitored object; wherein, ε HbR (λ i )and Deoxygenated hemoglobin and oxygenated hemoglobin are 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 currently set position of the monitored object; HbO2 and HbR represent the concentration of oxygenated hemoglobin and deoxygenated hemoglobin, respectively.

Images