An imaging method, device and electronic equipment for an intravascular lesion structure

Abstract

The application relates to the technical field of medical images, in particular to an imaging method and device for an intravascular lesion structure and an electronic device. The method comprises the following steps: controlling a second catheter end of a catheter to extend into a blood vessel with a lesion structure; controlling a laser light source to send laser light to a first catheter end, so that the laser light is transmitted to the lesion structure through a laser optical fiber; in response to the fact that multiple optical fiber sensors receive ultrasonic waves, determining ultrasonic wave information of the ultrasonic waves received by each optical fiber sensor; wherein the ultrasonic waves are emitted by the lesion structure after absorbing the laser light; and determining an image of the lesion structure according to the ultrasonic wave information. The application can solve the technical problem that the existing imaging method for the intravascular lesion structure has a greater negative impact on patients and a poor imaging effect.

Description

Technical Field

[0001] This application relates to the field of medical imaging technology, and in particular to an imaging method, device, and electronic device for intravascular lesion structures. Background Technology

[0002] Based on existing medical experience, calcified plaques in blood vessels can cause the blood vessel walls to harden and lose elasticity, leading to cardiovascular events such as angina and myocardial infarction, and may even eventually cause complete occlusion of blood vessels, resulting in acute ischemic symptoms.

[0003] In practice, calcified plaques are usually ablated by sending high-energy lasers into the blood vessel through a catheter containing a laser fiber. This operation requires determining the location of the calcified plaques within the blood vessel. In existing technologies, contrast agents can be injected intravenously into the blood vessel to enhance the contrast between the blood vessel and the surrounding tissues, allowing the shape of the calcified plaques to be clearly seen in medical imaging such as CT (Computed Tomography) images.

[0004] In practical applications, although the angiography methods mentioned above can determine the shape of calcified plaques, contrast agents may cause a variety of allergic reactions, including itching, urticaria, angioedema, bronchospasm, hypotension, and syncope. In addition, intravascular ultrasound images can display cross-sectional images of blood vessels, but can only image from the side and not from the front. Therefore, it can be seen that existing imaging methods for intravascular lesions have technical problems that have many negative impacts on patients and poor imaging results. Summary of the Invention

[0005] In view of this, the purpose of this application is to provide an imaging method, device and electronic device for intravascular lesion structures, so as to solve the technical problem that existing imaging methods for intravascular lesion structures have many negative impacts on patients.

[0006] In a first aspect, this application provides an imaging method for intravascular lesions, applied to an imaging device for intravascular lesions. The device includes a laser source and a catheter, the laser source being connected to a first catheter tip of the catheter. The catheter includes a laser fiber and multiple fiber optic sensors disposed within its wall. The method includes:

[0007] The second catheter tip of the catheter is controlled to extend into a blood vessel with a diseased structure;

[0008] The laser source is controlled to send a laser beam to the end of the first catheter, so that the laser beam is transmitted to the lesion structure through the laser fiber.

[0009] In response to the receipt of ultrasonic waves by the plurality of optical fiber sensors, ultrasonic information of the ultrasonic waves received by each of the optical fiber sensors is determined;

[0010] The ultrasound waves are emitted by the lesion structure after absorbing the laser.

[0011] Based on the ultrasound information, an image of the lesion structure is determined.

[0012] Secondly, this application provides an imaging device for intravascular lesion structures. The device includes a laser source, a catheter, and a terminal device. The laser source is connected to the first catheter end of the catheter. The catheter includes a laser fiber and multiple fiber optic sensors disposed within the catheter wall. The terminal device includes a control module, an information module, and an image module.

[0013] The control module is used to control the second catheter tip of the catheter to extend into a blood vessel with a lesion structure;

[0014] The control module is also used to control the laser source to send laser light to the end of the first catheter, so that the laser light is transmitted to the lesion structure through the laser fiber;

[0015] The information module is used to determine the ultrasonic information received by each of the multiple fiber optic sensors in response to the receipt of ultrasonic waves.

[0016] The ultrasound waves are emitted by the lesion structure after absorbing the laser.

[0017] The image module is used to determine an image of the lesion structure based on the ultrasound information.

[0018] Thirdly, this application provides an electronic device including a processor and a memory, the memory being used to store an application program, and the processor enabling the electronic device to implement the above-described imaging method for intravascular lesions by running or executing a software program stored in the memory.

[0019] Fourthly, this application provides a computer-readable storage medium for storing program code executed by a processor, the program code being used to implement the above-described imaging method for intravascular lesion structures.

[0020] Beneficial effects:

[0021] This application provides an imaging method for intravascular lesions, applicable to an imaging device for intravascular lesions. The device includes a laser source and a catheter. The laser source is connected to a first catheter tip. The catheter includes a laser fiber and multiple fiber optic sensors disposed within its wall. The method includes: controlling a second catheter tip to extend into a blood vessel with a lesion; controlling the laser source to send laser light to the first catheter tip, so that the laser light is transmitted to the lesion through the laser fiber; determining the ultrasound information received by each fiber optic sensor in response to ultrasound waves received by the multiple fiber optic sensors; wherein the ultrasound waves are emitted by the lesion after absorbing the laser light; and determining an image of the lesion based on a target time and multiple reception times.

[0022] In summary, this application fully utilizes the physical characteristics of the lesion structure and provides an automated imaging technology that does not require the use of contrast agents. The image of the lesion structure can be determined at any time according to actual needs. Therefore, the imaging method provided by this application has the advantages of safety and speed, and can solve the technical problem that existing imaging methods for intravascular lesions have many negative impacts on patients. Attached Figure Description

[0023] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the embodiments of this application will be briefly introduced below. The following drawings only show some embodiments of this application and should not be regarded as a limitation of the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.

[0024] Figure 1 This is a schematic diagram of the imaging device for intravascular lesion structures provided in an embodiment of this application;

[0025] Figure 2 A cross-sectional view of the catheter provided in an embodiment of this application in a direction perpendicular to the length extension direction;

[0026] Figure 3 A schematic flowchart illustrating the imaging method for intravascular lesion structures provided in an embodiment of this application;

[0027] Figure 4 A schematic diagram of the structure of a Bragg grating provided in an embodiment of this application;

[0028] Figure 5 Example diagram of the spectrum of the merged reflected light provided in the embodiments of this application;

[0029] Figure 6 A schematic diagram of an optical fiber looper, wavelength division multiplexer, and demodulator provided in an embodiment of this application;

[0030] Figure 7 A schematic flowchart of the Sagnac interferometric demodulation method provided in an embodiment of this application;

[0031] Figure 8 This application provides schematic diagrams illustrating the relationship between wavelength and energy ratio, and the relationship between wavelength and demodulated output value.

[0032] Figure 9 This is a schematic diagram of the terminal device in the imaging apparatus for intravascular lesions provided in the embodiments of this application. Detailed Implementation

[0033] In existing technologies, the contrast agents used in angiography may cause various allergic reactions, including itching, urticaria, angioedema, bronchospasm, hypotension, and syncope. In addition, the contrast agent's imaging time is relatively short. If the calcified plaques in the blood vessels are large or numerous, multiple injections of contrast agent and multiple CT images may be required, which may lead to excessive radiation exposure for the patient. This is especially true for coronary angiography, which requires multi-angle and high-frame-rate imaging. Therefore, the risks of angiography cannot be ignored. Furthermore, while ultrasound images of blood vessels can display cross-sectional images, they can only show the side view and cannot image the front.

[0034] In summary, existing imaging methods for intravascular lesions have technical problems such as causing many negative impacts on patients and poor imaging results.

[0035] To address the aforementioned technical problems, this application provides an imaging method, apparatus, and electronic device for intravascular lesions. To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of this application will be clearly and completely described below in conjunction with the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this application. All other embodiments obtained by those skilled in the art based on the embodiments of this application without creative effort are within the scope of protection of this application.

[0036] First, this application provides an imaging method for intravascular lesion structures, applicable to imaging devices for intravascular lesion structures, such as... Figure 1 and Figure 2 As shown, Figure 1 This is a schematic diagram of the imaging device for intravascular lesion structures provided in an embodiment of this application. Figure 2The cross-sectional view of the conduit provided in this application embodiment is shown in a direction perpendicular to its length extension direction. The device includes: a conduit 100, a laser source 210, a first coupler 220, a broadband source 310, an optical fiber looper 320, a second coupler 330, an optical fiber splitter 340, a wavelength division multiplexer 410, a demodulator 420, a photodetector 430, a digital-to-analog converter 440, and a terminal device 500. The conduit 100 includes: a tube wall 110, a laser fiber 120 disposed within the tube wall 110, an optical fiber sensor 130, and a guide wire 140. The laser fiber 120, the optical fiber sensor 130, and the guide wire 140 all extend along the length extension direction of the tube wall 110.

[0037] The imaging method for intravascular lesions will now be described in detail using imaging devices for intravascular lesions, such as... Figure 3 As shown, Figure 3 This is a schematic flowchart of an imaging method for intravascular lesions provided in an embodiment of this application. The method includes steps S100 to S400, as detailed below:

[0038] S100: The second catheter tip of the control catheter extends into a blood vessel with a diseased structure.

[0039] Specifically, in practice, it is necessary to obtain images of intravascular lesions in many situations. For example, during laser treatment of lesions, it is necessary to continuously monitor the shape and size of the lesions to determine the progress of the laser treatment.

[0040] In this embodiment, the lesion structure is a structure that occurs within a blood vessel, needs to be removed, and will generate ultrasound waves after being received and connected to a catheter, such as calcified plaques and hemangiomas.

[0041] In this embodiment, the tube wall 110 of the catheter 100 provides support and protection for other structures within the catheter 100; the laser fiber 120 transmits the laser emitted by the laser source 210 to the lesion structure within the blood vessel, where the lesion structure absorbs the laser energy and undergoes thermoelastic expansion to generate ultrasound; the fiber optic sensor 130 receives the ultrasound emitted by the lesion structure, and there are usually multiple fiber optic sensors 130; the guide wire 140 is mainly used to guide the catheter 100 into the blood vessel and assist the catheter 100 in passing through obstacles such as tortuosity, calcification, stenosis, or collateral circulation to reach the vicinity of the lesion structure; wherein, the end of the catheter 100 connected to the laser source 210 in the length extension direction is the first catheter end, and the end in the length extension direction for extending into the blood vessel is the second catheter end.

[0042] In actual operation, the purpose of inserting the second catheter tip of the control catheter into the blood vessel with the lesion structure is to carry the laser fiber 120 and the fiber optic sensor 130 to the vicinity of the lesion structure.

[0043] In one implementation, the first fiber optic end of each fiber optic sensor 130 is connected to a broadband light source 310; the second fiber optic end of each fiber optic sensor 130 for insertion into the blood vessel is equipped with a Bragg grating, which is used to receive ultrasound waves; before S100, the method further includes step (1), as detailed below:

[0044] Step (1): Control the broadband light source to send broadband light to the first fiber end of each fiber sensor, so that the broadband light is transmitted to the corresponding Bragg grating through each fiber sensor.

[0045] Among them, the Bragg grating generates reflected light after receiving broadband light, and different Bragg gratings produce reflected light with different wavelengths.

[0046] Specifically, in the prior art, a broadband light source 310 refers to a light source with a wide spectral range. The broadband light source 310 can emit continuous light within a relatively wide wavelength range. In the embodiments of this application, the light beam emitted by the broadband light source 310 is named broadband light.

[0047] In this embodiment of the application, the portions of all the fiber optic sensors 130 near the second fiber end are fused together to form a 1xN fiber optic splitter 340, which is used to uniformly distribute broadband light to multiple fiber optic sensors 130 until it reaches the second fiber end of the fiber optic sensor 130.

[0048] In this embodiment, the broadband light source 310 is connected to the terminal device 500 for communication. The terminal device 500 can control the timing and duration of broadband light transmission by the broadband light source 310. The broadband light enters the fiber optic sensor 130 from the end of the first fiber and then reaches the Bragg grating located at the end of the second fiber. After receiving the broadband light, the light with a wavelength equal to twice the product of the grating pitch of the Bragg grating and the core refractive index of the fiber optic sensor 130 is reflected by the Bragg grating to produce narrowband reflected light, while light of other wavelengths is almost unaffected and continues to be transmitted through the Bragg grating.

[0049] In summary, a Bragg grating can only reflect light of a specific wavelength. Once the grating pitch of the Bragg grating is determined, the wavelength of the reflected light it can reflect can also be determined accordingly. In other words, the Bragg grating that emits the reflected light can also be determined based on the wavelength of the reflected light. In the embodiments of this application, since different Bragg gratings produce different wavelengths of reflected light, there is a one-to-one correspondence between the Bragg grating, the grating pitch of the Bragg grating, and the wavelength of the reflected light it can reflect.

[0050] It is important to emphasize that the emission of broadband light is continuous. In practice, multiple lasers are usually sent during the continuous emission of broadband light to determine multiple images of the lesion structure.

[0051] In one implementation, before S100, the method further includes steps (2) to (4), as detailed below:

[0052] Step (2): Determine the number of fiber optic sensors and Bragg gratings to be configured in the catheter based on the target accuracy of the lesion structure image.

[0053] Specifically, in the embodiments of this application, the target accuracy of an image refers to the accuracy that the image needs to achieve. Accuracy can be other indicators that indicate image quality, such as image sharpness. The target accuracy can be determined according to actual needs, and this application does not impose any specific limitations on it.

[0054] In this embodiment, the more fiber optic sensors and Bragg gratings there are, the more information about the lesion structure can be obtained, and thus a clearer image of the lesion structure can be obtained. In actual operation, the quantitative correspondence between the accuracy and the number of fiber optic sensors 130 and Bragg gratings can be determined according to actual needs, and this application does not make specific limitations on this.

[0055] Step (3): At the end of the target number of fiber optic sensors, configure Bragg gratings with different grating pitches.

[0056] Specifically, once the target quantity is determined, the target quantity of fiber optic sensors 130 can be prepared, and a Bragg grating can be configured at one end of each fiber optic sensor 130; for example... Figure 4 As shown, Figure 4 This is a schematic diagram of the structure of a Bragg grating provided in an embodiment of this application.

[0057] Step (4): The fiber optic sensor equipped with the Bragg grating is placed in the conduit according to the preset arrangement.

[0058] Specifically, after configuring Bragg gratings at the ends of each fiber optic sensor 130, the fiber optic sensors 130 can be arranged in the conduit 100 according to a preset arrangement.

[0059] In the embodiments of this application, the preset arrangement pattern can be determined according to actual needs. This application does not limit this. In actual operation, the preset arrangement pattern can be to arrange the target number of fiber optic sensors 130 at equal intervals in the tube wall 110 of the conduit 100. If the target number is large, the target number of fiber optic sensors 130 can be stacked.

[0060] S200: Controls the laser source to send laser light to the end of the first catheter so that the laser light is transmitted to the lesion structure through the laser fiber.

[0061] Specifically, in this embodiment, the laser source 210 is communicatively connected to the terminal device 500, and the terminal device 500 can control the laser source 210 to send laser light. The laser light is transmitted through the laser fiber 120 and then directly hits the lesion structure. In this embodiment, the laser fiber 120 can be a single multimode fiber or multiple single-mode fibers. The laser fiber 120 is also equipped with a first coupler 220, which controls the transmission direction, intensity and wavefront characteristics of the laser, thereby improving the transmission efficiency and quality of the laser.

[0062] It is important to emphasize that the laser emission is not continuous, but only required when imaging or ablation of the diseased structure is needed.

[0063] In one implementation, S200 includes step (5), as detailed below:

[0064] Step (5): Control the laser source to send laser light to the end of the first conduit at the target time.

[0065] Specifically, in this embodiment, the laser source 210 emits laser light at a set time (i.e., a target time), where "target" means pre-specified. In actual operation, the laser can be emitted at a fixed time, such as 20:30:00, or at a set frequency, such as every 2 seconds. Since both methods allow for "pre-specifying" the time of each laser emission, this is equivalent to "the laser source 210 emitting laser light at the target time." S300: In response to multiple fiber optic sensors receiving ultrasonic waves, determine the ultrasonic information received by each fiber optic sensor.

[0066] Ultrasound is emitted by the diseased structure after absorbing laser light.

[0067] Specifically, in actual operation, since the lesion structure is usually an irregular polyhedron and the surface may have uneven structural features, when multiple laser beams are received at different surface positions of the lesion structure and corresponding ultrasound waves are emitted, the ultrasound wave information will characterize the information of different surface positions. The information of different surface positions is helpful in determining the image of the lesion structure. Therefore, the ultrasound wave information can be determined immediately after receiving the ultrasound wave, which can be used to determine the image of the lesion structure in subsequent steps.

[0068] In one implementation, the ultrasonic information is the moment when the fiber optic sensor receives the ultrasonic wave; since the laser source 210 emits laser light uniformly towards the lesion structure at the target time, the moment when the ultrasonic wave emitted by the lesion structure is received can indicate the distance between the fiber optic sensor 130 and the lesion structure.

[0069] In one implementation, S300 includes steps (6) to (7), as detailed below:

[0070] Step (6): While the broadband light source continuously emits broadband light and the Bragg grating continuously generates reflected light, monitor whether the spectrum of the reflected light generated by each Bragg grating shows a shift that meets the preset standard.

[0071] Specifically, when the broadband light source 310 continuously transmits broadband light and the Bragg grating continuously generates reflected light, since the length of the second end of the fiber optic sensor 130 changes after receiving the ultrasonic wave, the grating pitch of the Bragg grating also changes. Therefore, the spectrum of the reflected light reflected by the Bragg grating shows a shift that conforms to a preset standard. Thus, it can be determined whether the fiber optic sensor 130 has received the ultrasonic wave by monitoring whether the spectrum of the reflected light generated by each Bragg grating shows a shift that conforms to a preset standard.

[0072] In actual operation, the reflected light from multiple fiber optic sensors 130 is combined at the fiber optic splitter 340, such as... Figure 5 and Figure 6 As shown, Figure 5 This is an example diagram of the spectrum of the merged reflected light provided in an embodiment of this application. Figure 6 This is a schematic diagram of the fiber optic looper, wavelength division multiplexer, and demodulator provided in the embodiments of this application. Figure 5 It can be seen that the spectrum of the merged reflected light is comb-like.

[0073] Step (7): If the spectrum of the reflected light generated by the Bragg grating shows a shift that meets the preset standard, the moment when the spectrum shows a shift that meets the preset standard is determined as the receiving moment.

[0074] The shift in the spectrum of the reflected light is caused by the ultrasonic waves transmitted to the Bragg grating.

[0075] Specifically, such as Figure 1 As shown, the fiber optic sensor 130 is also equipped with a second coupler 330. The second coupler 330 controls the transmission direction, intensity and wavefront characteristics of the combined reflected light, thereby improving the transmission efficiency and quality of the combined reflected light. After the combined reflected light passes through the second coupler 330 and the fiber optic looper 320 in sequence, it is transmitted to the wavelength division multiplexer 410.

[0076] In this embodiment, wavelength division multiplexer 410 is used to distribute reflected light from different fiber optic sensors 130 to each demodulator 420. The demodulator 420 demodulates the reflected light to obtain an optical signal. The optical signal passes through photodetector 430 and digital-to-analog converter 440 in sequence to obtain a digitized optical signal. The optical signal is transmitted to terminal device 500, and terminal device 500 determines the spectrum corresponding to the optical signal based on the optical signal.

[0077] In actual operation, since broadband light is continuously transmitted, the spectrum transmitted to the terminal device 500 is continuous. When the fiber optic sensor 130 does not receive an ultrasonic signal, the spectrum is stable. If the fiber optic sensor 130 receives an ultrasonic wave, it will cause the spectrum of the reflected light reflected by the Bragg grating to shift in accordance with a preset standard. The terminal device 500 can accurately determine the moment when the shift in accordance with the preset standard occurs and determine it as the receiving moment accordingly.

[0078] like Figure 7 As shown, Figure 7 This is a schematic flowchart of the Sagnac interferometric demodulation method provided in this application embodiment. The demodulation of the merged reflected light can be performed using an edge filtering algorithm or the Sagnac interferometric demodulation method. Taking the Sagnac interferometric demodulation method as an example, the modulated reflected light from the wavelength division multiplexer 410 is split into two beams, clockwise and counterclockwise, by the fiber optic looper 320 and the second coupler 330, and enters the Sagnac loop. The light in the two directions is reflected at different depths of the linear chirped grating (a Bragg grating with a gradually changing grating pitch), causing a change in the phase difference between the two beams, which is wavelength-dependent. The reflected light in the two directions interferes with the incident light at the second coupler 330, and is then output from the fiber optic looper 320 and the second coupler 330, respectively.

[0079] Both demodulation methods produce two beams of light, such as Figure 8 As shown, Figure 8 This application provides schematic diagrams illustrating the relationship between wavelength and energy ratio, and the relationship between wavelength and demodulated output value, in its embodiments. Figure 8 The curve on the left side of the diagram illustrates the relationship between wavelength and energy ratio. Figure 8 The curve on the right side of the graph is a schematic diagram showing the relationship between wavelength and demodulated output value. Figure 7 and Figure 8It can be seen that the response curves of the reflected light / broadband light energy ratio and the reflected light wavelength are complementary for the two optical paths. The energy of the two beams is measured by photodetector 430 and digital-to-analog converter 440, respectively, and recorded as P1 and P2. The demodulated output value is equal to (P1-P2) / (P1+P2). This output value has an approximately linear relationship with the reflected wavelength. Therefore, the change in the output value reflects the change in the length of the second fiber end of the fiber optic sensor 130, which is the change in the sound pressure of the ultrasonic signal.

[0080] S400: Determine the image of the lesion structure based on ultrasound information.

[0081] Specifically, as discussed above, the ultrasound information of different ultrasound waves can characterize the information of different surface positions in the lesion structure. Therefore, after accumulating enough ultrasound information, the information of multiple surface positions of the lesion structure can be determined based on the ultrasound information, and subsequently, the image of the lesion structure can be determined based on the information of multiple surface positions.

[0082] In one implementation, S400 includes step (8), as detailed below:

[0083] Step (8): Determine the image of the lesion structure based on the target time and multiple receiving times.

[0084] Specifically, in the embodiments of this application, both the target time and the receiving time can be accurately determined. The purpose of determining the target time is to determine the time when the lesion structure receives the laser, and the purpose of determining the receiving time is to determine the time when the fiber optic sensor 130 receives the ultrasound. However, both of the above cannot be directly measured and can only be obtained indirectly.

[0085] In actual operation, the timing of laser emission from laser source 210 can be precisely controlled. Furthermore, since the time required for the laser to travel within laser fiber 120 and through the bloodstream can also be determined, the timing of laser reception by the lesion structure can be determined based on this target timing and the time required for the laser to travel within laser fiber 120 and through the bloodstream. Additionally, the reflected light emitted by fiber optic sensor 130 is converted into an optical signal via fiber optic splitter 340, etc., and the terminal device 500 determines the corresponding spectrum based on this optical signal. Therefore, the timing of ultrasound reception by fiber optic sensor 130 can be determined based on this reception timing and the time required for the reflected light or optical signal to travel through the structure of fiber optic splitter 340, etc. The time required for the laser to travel within laser fiber 120 and through the bloodstream, as well as the time required for the reflected light or optical signal to travel through the structure of fiber optic splitter 340, etc., can all be determined empirically or measured by instruments; this application does not impose specific limitations on this.

[0086] In one implementation, step (8) includes steps (8.1) to (8.2), as detailed below:

[0087] Step (8.1): For each Bragg grating in the multiple Bragg gratings, determine the distance between each Bragg grating and the lesion structure based on the target time, the corresponding reception time, and the propagation speed of the received ultrasound in the blood.

[0088] Specifically, in the embodiments of this application, after determining the target time and multiple receiving times, the time difference between the receiving time and the target time can be determined for each receiving time, and the distance between the ultrasound signal transmitted from the lesion structure to the fiber optic sensor 130 in the blood can be obtained by subtracting the time consumed.

[0089] Step (8.2): Determine the three-dimensional image of the lesion structure based on multiple distances.

[0090] Specifically, in this embodiment, since the relative positions between each fiber optic sensor 130 are fixed and the wavelength of the reflected light that each fiber optic sensor 130 can reflect is also fixed, once multiple "distances" are determined, a three-dimensional image of the lesion structure can be determined based on the aforementioned multiple "distances".

[0091] In actual operation, for each fiber optic sensor 130, a corresponding "distance" will be obtained. The greater the "distance", the more detailed the three-dimensional image can be.

[0092] In practical applications, such as during laser treatment of diseased structures, the laser source 210 can be controlled to emit lasers at preset intervals. After the laser is emitted, an image of the diseased structure can be obtained, which can be used to quickly and accurately determine the progress of laser treatment.

[0093] Second, this application provides an imaging device for intravascular lesions, the device including a laser source, a catheter, and a terminal device. The laser source is connected to the first catheter tip of the catheter, and the catheter includes a laser fiber and multiple fiber optic sensors disposed within the catheter wall; Figure 9 As shown, Figure 9 This is a schematic diagram of the structure of the terminal device in the imaging device for intravascular lesion structures provided in the embodiments of this application. The terminal device includes: a control module 500, an information module 600, and an image module 700.

[0094] The control module 500 is used to control the insertion of the second catheter tip of the catheter into a blood vessel with a diseased structure.

[0095] The control module 500 is also used to control the laser source to send laser to the end of the first catheter so that the laser is transmitted to the lesion structure through the laser fiber;

[0096] Information module 600 is used to determine the ultrasonic information of each ultrasonic wave received by multiple fiber optic sensors in response to the receipt of ultrasonic waves by multiple fiber optic sensors.

[0097] Among them, ultrasound is emitted by the diseased structure after absorbing laser light;

[0098] Image module 700 is used to determine images of lesion structures based on ultrasound information.

[0099] In one implementation, the ultrasonic information is the reception time of the ultrasonic wave received by the fiber optic sensor; the control module 500 is further configured to control the laser source to send a laser to the end of the first conduit at a target time.

[0100] The information module 600 is further configured to determine an image of the lesion structure based on the target time and multiple receiving times. In one implementation, the control module 500 is further configured to control the laser source to send laser light to the end of the first catheter, so that the laser light is transmitted through the laser fiber to the lesion structure to perform ablation treatment on the lesion structure.

[0101] Specifically, in actual operation, the laser emitted by the laser source 210 not only has the function of causing the lesion structure to emit ultrasound after receiving it, but also can directly erode the lesion structure, causing the lesion structure in the blood vessel to continuously shrink. Therefore, the imaging device for lesion structure in blood vessels provided in this application embodiment not only has the function of imaging the lesion structure, but also has the function of erode the lesion structure. Therefore, when the imaging device for lesion structure in blood vessels provided in this application embodiment is applied, it is possible to continuously observe the shape change of the lesion structure while performing erode treatment on the lesion structure in blood vessels, so as to adjust the intensity and duration of the laser emitted into the blood vessel in real time. Therefore, the imaging device for lesion structure in blood vessels provided in this application embodiment helps to improve the efficiency and accuracy of erode treatment on the lesion structure.

[0102] In one implementation, the first fiber end of each fiber sensor is connected to a broadband light source; the second fiber end of each fiber sensor for insertion into the blood vessel is equipped with a Bragg grating, which is used to receive ultrasound waves.

[0103] The control module 500 is also used to control the broadband light source to send broadband light to the first fiber end of each fiber sensor, so that the broadband light is transmitted to the corresponding Bragg grating through each fiber sensor.

[0104] Among them, the Bragg grating generates reflected light after receiving broadband light, and different Bragg gratings produce reflected light with different wavelengths.

[0105] In one implementation, the terminal device further includes: a configuration module;

[0106] The configuration module is used to determine the number of fiber optic sensors and Bragg gratings to be configured in the catheter based on the target accuracy of the image of the lesion structure.

[0107] The configuration module is also used to configure Bragg gratings with different grating pitches at the ends of a target number of fiber optic sensors.

[0108] The configuration module is also used to place fiber optic sensors equipped with Bragg gratings inside the conduit according to a preset arrangement.

[0109] In one implementation, the information module 600 is further configured to monitor whether the spectrum of the reflected light generated by each Bragg grating deviates from a preset standard when the broadband light source continuously transmits broadband light and the Bragg grating continuously generates reflected light.

[0110] The information module 600 is also used to determine the moment when the spectrum of the reflected light generated by the Bragg grating deviates from the preset standard as the receiving moment if the spectrum deviates from the preset standard.

[0111] The shift in the spectrum of the reflected light is caused by the ultrasonic waves transmitted to the Bragg grating.

[0112] In one implementation, the image module 700 is further configured to determine the distance between each Bragg grating and the lesion structure based on the target time, the corresponding reception time, and the propagation speed of the received ultrasound in the blood.

[0113] The image module 700 is also used to determine a three-dimensional image of the lesion structure based on multiple distances.

[0114] Third, this application also provides an electronic device, including a memory, a processor, and a computer program stored in the memory and executable on the processor. When the processor executes the computer program, it implements the steps S100 to S400 provided in the above embodiments.

[0115] Fourth, this application also provides a computer-readable storage medium storing a computer program, wherein the computer program is executed by a processor to perform the steps of S100 to S400 of the above embodiments.

[0116] Fifth, the computer program product provided in this application includes a computer-readable storage medium storing program code. The instructions included in the program code can be used to execute the methods in the preceding method embodiments. For specific implementation, please refer to the steps of S100 to S400 of the method embodiments, which will not be repeated here.

[0117] In the embodiments provided in this application, it should be understood that the disclosed apparatus and methods can be implemented in other ways. The apparatus embodiments described above are merely illustrative. For example, the division of units is only a logical functional division, and in actual implementation, there may be other division methods. Furthermore, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Additionally, the displayed or discussed mutual couplings, direct couplings, or communication connections may be through some communication interfaces; indirect couplings or communication connections between devices or units may be electrical, mechanical, or other forms.

[0118] Furthermore, the units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.

[0119] Furthermore, the functional modules in the various embodiments of this application can be integrated together to form an independent part, or each module can exist independently, or two or more modules can be integrated to form an independent part.

[0120] It should be noted that if the function is implemented as a software module and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, a server, or a network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of this application. The aforementioned storage medium includes various media capable of storing program code, such as USB flash drives, portable hard drives, read-only memory (ROM), random access memory (RAM), magnetic disks, or optical disks.

[0121] In this document, relational terms such as first and second are used only to distinguish one entity or operation from another entity or operation, without necessarily requiring or implying any such actual relationship or order between these entities or operations.

[0122] The above description is merely an embodiment of this application and is not intended to limit the scope of protection of this application. Various modifications and variations can be made to this application by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the scope of protection of this application.

Claims

1. An imaging method for intravascular lesion structures, characterized in that, An imaging device for intravascular lesions, the device comprising a laser source and a catheter, the laser source being connected to a first catheter tip of the catheter, the catheter including a laser fiber and multiple fiber optic sensors disposed within the catheter wall; the method comprising: The second catheter tip of the catheter is controlled to extend into a blood vessel with a diseased structure; The laser source is controlled to send a laser beam to the end of the first catheter, so that the laser beam is transmitted to the lesion structure through the laser fiber. In response to the receipt of ultrasonic waves by the plurality of optical fiber sensors, ultrasonic information of the ultrasonic waves received by each of the optical fiber sensors is determined; The ultrasound waves are emitted by the lesion structure after absorbing the laser. Based on the ultrasound information, an image of the lesion structure is determined.

2. The method according to claim 1, characterized in that, The ultrasonic information is the reception time of the ultrasonic wave received by the fiber optic sensor; controlling the laser source to send laser light to the end of the first conduit includes: The laser source is controlled to send a laser beam to the end of the first conduit at the target time; Determining the image of the lesion structure based on the ultrasound information includes: An image of the lesion structure is determined based on the target time and multiple receiving times.

3. The method according to claim 2, characterized in that, Each of the fiber optic sensors has its first fiber end connected to a broadband light source; each of the fiber optic sensors has its second fiber end, which is used to extend into the blood vessel, equipped with a Bragg grating for receiving the ultrasound waves. Before the second catheter tip controlling the catheter is inserted into a blood vessel with a diseased structure, the method further includes: The broadband light source is controlled to send broadband light to the first fiber end of each of the fiber sensors, so that the broadband light is transmitted to the corresponding Bragg grating through each of the fiber sensors. The Bragg grating generates reflected light after receiving the broadband light, and the wavelength of the reflected light generated by different Bragg gratings is different.

4. The method according to claim 3, characterized in that, Before controlling the broadband light source to transmit broadband light to the first fiber ends of each of the fiber optic sensors, the method further includes: Based on the target accuracy of the image of the lesion structure, determine the target number of the fiber optic sensor and the Bragg grating to be configured in the catheter; At the ends of the target number of optical fiber sensors, Bragg gratings with different grating pitches are configured; The fiber optic sensor equipped with the Bragg grating is arranged inside the conduit according to a preset pattern.

5. The method according to claim 3, characterized in that, The step of determining the reception time of the ultrasonic wave received by each of the multiple fiber optic sensors in response to the receipt of the ultrasonic wave includes: When the broadband light source continuously emits broadband light and the Bragg grating continuously generates reflected light, monitor whether the spectrum of the reflected light generated by each Bragg grating shows a shift that meets a preset standard; If the spectrum of the reflected light generated by the Bragg grating shows a shift that conforms to the preset standard, the moment when the spectrum shows a shift that conforms to the preset standard is determined as the receiving moment; The shift in the spectrum of the reflected light is caused by the ultrasonic waves transmitted to the Bragg grating.

6. The method according to claim 3, characterized in that, Determining the image of the lesion structure based on the target time and multiple receiving times includes: For each of the multiple Bragg gratings, the distance between each Bragg grating and the lesion structure is determined based on the target time, the corresponding receiving time, and the propagation speed of the received ultrasound in the blood. A three-dimensional image of the lesion structure is determined based on multiple distances.

7. An imaging device for intravascular lesions, characterized in that, The device includes a laser source, a conduit, and a terminal device. The laser source is connected to the first end of the conduit. The conduit includes a laser fiber and multiple fiber optic sensors disposed within the conduit wall. The terminal device includes a control module, an information module, and an image module. The control module is used to control the second catheter tip of the catheter to extend into a blood vessel with a lesion structure; The control module is also used to control the laser source to send laser light to the end of the first catheter, so that the laser light is transmitted to the lesion structure through the laser fiber; The information module is used to determine the ultrasonic information received by each of the multiple fiber optic sensors in response to the receipt of ultrasonic waves. The ultrasound waves are emitted by the lesion structure after absorbing the laser. The image module is used to determine an image of the lesion structure based on the ultrasound information.

8. The apparatus according to claim 7, characterized in that, The ultrasonic information is the time when the optical fiber sensor receives the ultrasonic wave; the control module is also used to control the laser source to send laser light to the end of the first conduit at a target time. The information module is also used to determine the image of the lesion structure based on the target time and multiple receiving times.

9. The apparatus according to claim 7, characterized in that, The control module is also used to control the laser source to send laser light to the end of the first catheter, so that the laser light is transmitted to the lesion structure through the laser fiber to perform ablation treatment on the lesion structure.

10. An electronic device, characterized in that, The electronic device includes a processor and a memory, the memory being used to store an application program, and the processor enabling the electronic device to perform the imaging method for intravascular lesions as described in any one of claims 1 to 6 by running or executing a software program stored in the memory.

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