Photoacoustic endoscopy component, endoscopy probe and computer equipment

Abstract

The present application provides a photoacoustic endoscopy component, an endoscopy probe, and a computer device, which can not only perform photoacoustic endoscopy imaging, but also detect the rotation speed of the end of the endoscopy probe close to the detection tissue by means of laser, and adjust in real time according to the rotation speed to achieve high-quality photoacoustic imaging. The photoacoustic endoscopy component includes an endoscopy probe, a balloon, a rotary coupling device, a first light splitting module, a control unit, a display device, and a photoacoustic laser light source.

Description

Technical Field

[0001] The present application relates to the technical field of photoacoustic endoscopy, and in particular to a photoacoustic endoscopy component, an endoscopy probe and a computer device. Background Art

[0002] With the advancement of medical technology, people have an increasing demand for accurate diagnosis of early diseases. Photoacoustic endoscopic imaging technology has emerged in response to this demand. Photoacoustic endoscopic imaging technology generates ultrasonic signals by irradiating laser pulses onto tissues, causing a transient expansion effect caused by local heating. This ultrasonic signal can reflect the optical absorption characteristics of tissues, especially the concentration and oxygenation status of biological molecules such as hemoglobin. It has shown great potential in the fields of early cancer diagnosis, vascular imaging, tumor microenvironment monitoring, and especially minimally invasive imaging of internal organs such as the digestive tract and respiratory tract. However, in the actual detection process of existing technologies, the displayed images will be distorted or the resolution will be reduced. Summary of the invention

[0003] One advantage of the present application is that it provides a photoacoustic endoscopy component, an endoscopic probe, and a computer device, which can not only use lasers to influence the detected tissue to collect acoustic signals with information about the detected tissue, thereby displaying an image of the detected tissue based on the acoustic signals, but also use lasers to detect the rotational speed of one end of the endoscopic probe close to the detected tissue, and adjust in real time according to the rotational speed to achieve high-quality photoacoustic imaging.

[0004] Another advantage of the present application is to provide a photoacoustic endoscopy assembly, an endoscopy probe, and a computer device, wherein in order to achieve the above advantages, no expensive materials or complex structures are required in the present application. Therefore, the solution provided by the present application can successfully and effectively solve the above problems, and not only provides a simple photoacoustic endoscopy assembly, an endoscopy probe, and a computer device, but also increases the practicality and reliability of the photoacoustic endoscopy assembly.

[0005] Based on this, in order to achieve at least one of the above advantages or other advantages and purposes of the present application, the present application provides a photoacoustic endoscopy component, including:

[0006] An endoscopic probe, a balloon, a rotary coupling device, a first light splitting module, a control unit, a display device, and a photoacoustic laser light source;

[0007] One end of the photoacoustic laser light source is connected to the control unit, and the other end of the photoacoustic laser light source is connected to one end of the first light splitting module;

[0008] The other end of the first light splitting module is connected to the first end of the rotary coupling device, and is used to split the laser into a first light beam and a second light beam, and transmit the first light beam to the endoscope probe through the rotary coupling device;

[0009] The second end of the rotary coupling device is connected to the control unit, and the third end of the rotary coupling device is connected to the endoscope probe;

[0010] The endoscopic probe is arranged in the balloon, and the endoscopic probe can rotate inside the balloon driven by the rotary coupling device, and is used to influence the external detection tissue by means of the first light beam generated by the photoacoustic laser light source, so as to collect the acoustic signal with the detection tissue information, and transmit it to the control unit via the rotary coupling device, and the endoscopic probe is also used to detect the rotation speed of one end of the endoscopic probe close to the external detection tissue by using the first light beam, and transmit the optical signal with the rotation speed information to the control unit via the rotary coupling device and the first light splitting module in sequence;

[0011] The balloon has a hollow space;

[0012] The control unit is connected to the display device and is used to control the display device to display the image of the detected tissue according to the acoustic signal, and the control unit is also used to adjust one or more of the photoacoustic laser light source, the rotary coupling device and the display device according to the optical signal;

[0013] The display device is used to display the image of the detected tissue.

[0014] So configured, the present solution detects the rotational speed of one end of the endoscopic probe close to the external detection tissue by means of the first light beam, and transmits an optical signal carrying the rotational speed information to the control unit. The control unit adjusts one or more of the photoacoustic laser light source, the rotary coupling device and the display device according to the optical signal to clearly and accurately display the detection tissue.

[0015] According to one embodiment of the present application, the rotary coupling device includes a rotary motor and a coupler, the rotary motor is connected to the coupler, the rotary motor is used to drive the endoscope probe to rotate, and the coupler is used to transmit the signal through the rotary coupling device.

[0016] In this configuration, the rotary motor is used to drive the endoscopic probe to rotate, and the coupler is used as a signal transfer station to transmit the first light beam emitted by the first spectroscopic module to the endoscopic probe, and transmit the optical signal and the acoustic signal via the rotary coupling device to the control unit.

[0017] According to one embodiment of the present application, the control unit adjusts the image of the detected tissue by adjusting the repetition frequency of the photoacoustic laser light source, adjusting the rotation speed of the rotary motor, adjusting the acquisition data splicing algorithm, or a combination of the above three or any two.

[0018] With such a configuration, the signal synchronization unit can selectively adjust the repetition frequency of the photoacoustic laser light source with the aid of the laser control unit, adjust the rotation speed of the rotary motor with the aid of the rotary motor control unit, and adjust the data acquisition splicing algorithm with the aid of the data acquisition and processing unit according to the optical signal carrying the rotation speed information, by any one or a combination of these to more clearly and specifically display the detected tissue.

[0019] According to one embodiment of the present application, the balloon includes a balloon portion and a catheter, the catheter includes a front end detection segment and a rear end support segment, the front end detection segment is made of a transparent material for transmitting laser, the rear end support segment is made of an opaque material, a circular grating structure is arranged on the rear end support segment near the front end detection segment for encoding light.

[0020] With such arrangement, the circular grating structure is a structure that transmits light at equal intervals, and the rotation speed of the end of the endoscope probe close to the probed tissue can be determined according to the interval between two light transmissions.

[0021] According to one embodiment of the present application, the endoscopic probe includes: a trigger, an encoder, a transducer, and an optical fiber, and the trigger, encoder, and transducer are arranged at one end of the endoscopic probe close to the external detection tissue, the trigger is used to influence the external detection tissue with the help of the first light beam, the encoder is used to detect the rotation speed of one end of itself close to the external detection tissue with the help of the first light beam, the transducer is used to collect acoustic signals carrying detection tissue information, and the optical fiber is used to transmit the first light beam.

[0022] In this way, the optical fiber transmits the first light beam to the end of the endoscopic probe close to the external detection tissue, the trigger affects the external detection tissue with the help of the first light beam, the transducer collects the sound signal with the detection tissue information, and the encoder is used to detect the rotation speed of its own end close to the external detection tissue with the help of the first light beam.

[0023] According to one embodiment of the present application, the endoscopic probe further includes a second spectroscopic module and a reflector, wherein the second spectroscopic module is used to decompose the first light beam into a third light beam and a fourth light beam, and transmit the third light beam to the trigger, and transmit the fourth light beam to the encoder via reflection of the reflector, wherein the third light beam is a trigger light that affects the external detection tissue, and the fourth light beam is a detection light of the encoder.

[0024] In this arrangement, the third light beam is transmitted to the trigger to serve as a trigger light to irradiate the detection tissue, so that the detection tissue causes an instantaneous expansion effect due to the irradiation of the third light beam, thereby generating an ultrasonic signal. The fourth light beam serves as the detection light of the encoder to irradiate the circumferential grating structure of the balloon, thereby determining the rotation speed of the end of the endoscopic probe close to the detection tissue.

[0025] According to an embodiment of the present application, the endoscopic probe further includes a torque spring, and the torque spring is connected to the rotary coupling device, and is used to enable the rotary coupling device to drive the endoscopic probe to rotate.

[0026] According to one embodiment of the present application, the first spectroscopic module and the second spectroscopic module are dichroic mirrors. When the first spectroscopic module and the second spectroscopic module are dichroic mirrors, the endoscopic probe further includes an encoder light source, and the wavelength of light generated by the encoder light source is different from the wavelength of the laser generated by the photoacoustic laser light source.

[0027] According to one embodiment of the present application, the first light splitting module and the second light splitting module are beam splitters.

[0028] In this configuration, both the dichroic mirror and the beam splitter are optical elements, and are used to control the light in the optical path. The dichroic mirror can effectively reflect light of certain wavelengths and transmit light of other wavelengths, so an encoder light source is required. The wavelength of light generated by the encoder light source is different from the wavelength of the laser generated by the photoacoustic laser light source, thereby achieving the purpose of beam splitting; the beam splitter does not distinguish light based on the wavelength of light, but divides the incident light into two parts according to a certain ratio, one part is reflected and the other part is transmitted. The dichroic mirror or beam splitter can be selected according to different application environments.

[0029] In another aspect of the present application, an endoscopic probe is provided, which includes a spectroscopic module and an encoder. The spectroscopic module is used to decompose external light, and the encoder is used to detect the rotation speed of one end of the endoscopic probe close to the external detection tissue.

[0030] In another aspect of the present application, a computer device is provided, including a memory and a processor, wherein the memory stores a computer program, and when the processor executes the computer program, it can adjust the repetition frequency of an external photoacoustic laser light source, adjust the rotation speed of an external rotary motor, adjust one or more of the acquired data splicing algorithms to adjust the image of the external detected tissue.

[0031] Beneficial effects: The present application generates lasers of different wavelengths through a photoacoustic laser light source, and the laser is decomposed into a first light beam and a second light beam by a first spectroscopic module. The first light beam is transmitted to an endoscopic probe via a rotary coupling device, and the rotary coupling device also drives the endoscopic probe to rotate. The endoscopic probe uses the first light beam to affect the external detection tissue to collect the acoustic signal with the detection tissue information, and transmits it to the control unit via the rotary coupling device. The endoscopic probe also uses the first light beam to detect the rotation speed of one end of the endoscopic probe close to the external detection tissue, and transmits the optical signal with the rotation speed information to the control unit via the rotary coupling device and the first spectroscopic module in sequence. The control unit controls the display device to display the image of the detection tissue according to the acoustic signal, and the control unit also adjusts one or more of the photoacoustic laser light source, the rotary coupling device and the display device according to the optical signal. Thereby, on the basis of using laser to influence the detection tissue to collect acoustic signals carrying the detection tissue information, and then displaying the image of the detection tissue based on the acoustic signals, it is possible to detect the rotation speed of the end of the endoscopic probe close to the detection tissue with the help of the first light beam, and adjust one or more of the photoacoustic laser light source, the rotary coupling device and the display device in real time according to the rotation speed to achieve high-quality photoacoustic imaging. BRIEF DESCRIPTION OF THE DRAWINGS

[0032] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the conventional technology, the drawings required for use in the embodiments or the conventional technology descriptions are briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0033] Figure 1 A structural block diagram of a photoacoustic endoscopy component provided for one embodiment of the present application;

[0034] Figure 2 A structural block diagram of a photoacoustic endoscopy assembly according to the above embodiment of the present application is shown;

[0035] Figure 3 A schematic diagram of the optical path of the photoacoustic endoscopy assembly according to the above embodiment of the present application is shown;

[0036] Figure 4 A schematic structural diagram of a catheter in a photoacoustic endoscopy assembly according to the above embodiment of the present application is shown;

[0037] Figure 5 A schematic diagram of the optical path of a photoacoustic endoscopy assembly provided in another embodiment of the present application.

[0038] Figure numerals: 1. endoscopic probe; 11. second spectroscopic module; 12. trigger; 13. encoder; 14. transducer; 15. torque spring; 16. optical fiber; 17. reflector; 2. balloon; 21. catheter; 211. rear end support section; 2111. grating structure; 212. front end detection section; 22. capsule; 3. rotary coupling device; 31. rotary motor; 32. coupler; 4. first spectroscopic module; 5. control unit; 51. laser control unit; 52. photoelectric detection unit; 53. rotary motor control unit; 54. signal synchronization unit; 55. data acquisition and processing unit; 6. display device; 7. photoacoustic laser light source; 8. detection tissue; 901. encoder light source. DETAILED DESCRIPTION

[0039] In order to make the above-mentioned purposes, features and advantages of the present application more obvious and easy to understand, the specific implementation methods of the present application are described in detail below in conjunction with the accompanying drawings. In the following description, many specific details are set forth to facilitate a full understanding of the present application. However, the present application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar improvements without violating the connotation of the present application, so the present application is not limited by the specific embodiments disclosed below.

[0040] Considering that the existing technology can use laser to affect the detection tissue to collect acoustic signals with detection tissue information, so as to display the image of the detection tissue 8 based on the acoustic signals, during the actual detection process of the existing photoacoustic endoscopy component, the uniform rotation of the rotary motor 31 is transmitted to the front end of the endoscopic probe 1 in the catheter 21 through the torque spring 15, which will cause the rotation speed or angle of the probe head to change unevenly, thereby directly affecting the quality of the photoacoustic image, resulting in image distortion or resolution reduction. In order to solve this problem, the present application provides a photoacoustic endoscopy component, which can realize the use of laser to affect the detection tissue 8 to collect acoustic signals with detection tissue 8 information, so as to display the image of the detection tissue 8 based on the acoustic signals, and realize the detection of the rotation speed of the end of the endoscopic probe 1 close to the detection tissue 8 by means of the first light beam, and adjust one or more of the photoacoustic laser light source 7, the rotary coupling device 3 and the display device 6 in real time according to the rotation speed to achieve high-quality photoacoustic imaging.

[0041] For details, please refer to the attached Figures 1 to 3 An embodiment of the present application provides a photoacoustic endoscopy assembly, which may include an endoscopic probe 1, a balloon 2, a rotary coupling device 3, a first spectroscopic module 4, a control unit 5, a display device 6 and a photoacoustic laser light source 7.

[0042] More specifically, one end of the photoacoustic laser light source 7 is connected to the control unit 5, and the other end of the photoacoustic laser light source 7 is connected to one end of the first spectroscopic module 4, for generating lasers of different wavelengths according to the instructions of the control unit 5, and sending the lasers to the first spectroscopic module 4;

[0043] It should be noted that in this embodiment, the first light splitting module 4 and the second light splitting module 11 are illustrated by beam splitters.

[0044] The other end of the first light splitting module 4 is connected to the first end of the rotary coupling device 3, so as to decompose the laser into a first light beam and a second light beam, and transmit the first light beam to the endoscopic probe 1 through the rotary coupling device 3;

[0045] The second end of the rotary coupling device 3 is connected to the control unit 5, and the third end of the rotary coupling device 3 is connected to the endoscopic probe 1, so as to drive the endoscopic probe 1 to rotate and transmit the signal through the rotary coupling device 3;

[0046] The endoscopic probe 1 is arranged in the balloon 2. The endoscopic probe 1 can rotate inside the balloon 2 driven by the rotary coupling device 3, and is used to affect the external detection tissue 8 by means of the first light beam generated by the photoacoustic laser light source 7 and reflected by the first spectroscopic module 4, so as to collect the acoustic signal with the information of the detection tissue 8, and transmit it to the control unit 5 via the rotary coupling device 3. The endoscopic probe 1 is also used to detect the rotation speed of one end of itself close to the external detection tissue 8 by means of the first light beam, and transmit the optical signal with the rotation speed information to the control unit 5 via the rotary coupling device 3 and the first spectroscopic module 4 in sequence;

[0047] The balloon 2 has a hollow space for supporting the detection tissue 8;

[0048] The control unit 5 is connected to the display device 6 and is used to control the display device 6 to display the image of the detected tissue 8 according to the acoustic signal, and the control unit 5 is also used to adjust one or more of the photoacoustic laser light source 7, the rotary coupling device 3 and the display device 6 according to the optical signal;

[0049] The display device 6 is used to display the image of the detected tissue 8 based on the instruction of the control unit 5 .

[0050] It should be noted that the rotational speed of one end of the endoscopic probe 1 close to the external detection tissue 8 can be detected with the help of the first light beam, and an optical signal carrying the rotational speed information can be transmitted to the control unit 5. The control unit 5 adjusts one or more of the photoacoustic laser light source 7, the rotary coupling device 3 and the display device 6 according to the optical signal to clearly and accurately display the detection tissue 8.

[0051] It is worth noting that the rotary coupling device 3 includes a rotary motor 31 and a coupler 32. The rotary motor 31 is connected to the coupler 32. The rotary motor 31 is used to drive the endoscopic probe 1 to rotate. The coupler 32 is used to transmit the signal through the rotary coupling device 3, that is, as a signal transfer station, the first light beam emitted by the first splitting module 4 is transmitted to the endoscopic probe 1, and the optical signal and the acoustic signal through the rotary coupling device 3 are transmitted to the control unit 5.

[0052] It is worth noting that the control unit 5 selectively adjusts the repetition frequency of the photoacoustic laser light source 7 with the help of the laser control unit 51, adjusts the rotation speed of the rotary motor 31 with the help of the rotary motor control unit 53, and adjusts any one or a combination of the acquired data splicing algorithm with the help of the data acquisition and processing unit 55 according to the optical signal carrying the rotation speed information so as to display the image of the detected tissue 8 more clearly and explicitly.

[0053] It should be noted that the control unit 5 includes: a data acquisition and processing unit 55, a signal synchronization unit 54, a laser control unit 51, a photoelectric detection unit 52 and a rotary motor control unit 53. The signal synchronization unit 54 is connected to the data acquisition and processing unit 55, the laser control unit 51, the photoelectric detection unit 52 and the rotary motor control unit 53; and the laser control unit 51 is connected to the photoacoustic laser light source 7 to control the photoacoustic laser light source 7 to generate lasers of different wavelengths, the data acquisition and processing unit 55 is connected to the display device 6 to control the display device 6 to display the image of the detected tissue 8, and the rotary motor control unit 53 is connected to the rotary motor 31 to control the speed of the rotary motor 31. The photoelectric detection unit 52 is connected to the rotary coupling device 3 to receive the optical signal and send it to the signal synchronization unit 54. The signal synchronization unit 54 is used to selectively adjust the repetition frequency of the photoacoustic laser light source 7 with the help of the laser control unit 51, adjust the rotation speed of the rotary motor 31 with the help of the rotary motor control unit 53, and adjust any one or a combination of the acquired data splicing algorithm with the help of the data acquisition and processing unit 55 according to the optical signal received by the photoelectric detection unit 52, so as to more clearly and specifically display the image of the detected tissue 8.

[0054] Specifically, assuming that the rotation speed of the rotary motor 31 is set to w0, the repetition frequency of the photoacoustic laser light source 7 is n0 at this speed. If the instantaneous rotation speed of the head end of the endoscope probe 1 is measured to be w0+w1 by the encoder 13, the signal synchronization unit 54 can be fed back to the laser control unit 51 to increase the repetition frequency of the photoacoustic laser light source 7 to n0+n1, thereby increasing the excitation frequency and sampling frequency of the endoscope probe 1 at this time; or, the signal synchronization unit 54 can be fed back to the rotary motor control unit 53 to reduce the rotation speed of the rotary motor 31, thereby reducing the rotation speed of the head end of the endoscope probe 1; the signal synchronization unit 54 can also be fed back to the data acquisition processing unit 55 to adjust the splicing density of the acquired image data to achieve high-quality photoacoustic imaging; multiple of the above three methods can also be combined to adjust the image of the detected tissue 8.

[0055] Similarly, when the instantaneous rotational speed of the tip of the endoscopic probe 1 is measured to be w0-w2 by the encoder 13, the signal synchronization unit 54 can be used to feed back to the laser control unit 51 to reduce the repetition frequency of the photoacoustic laser light source 7 to n0-n2, thereby reducing the excitation frequency and sampling frequency of the endoscopic probe 1 at this time; or, the signal synchronization unit 54 can be used to feed back to the rotary motor control unit 53 to increase the rotational speed of the rotary motor 31, thereby increasing the rotational speed of the tip of the endoscopic probe 1; the signal synchronization unit 54 can also be used to feed back to the data acquisition processing unit 55 to adjust the splicing density of the acquired image data to achieve high-quality photoacoustic imaging; or, multiple of the above three methods can be combined to adjust the image of the detected tissue 8.

[0056] It should be noted that the implementation logic of the three implementation methods using any two of the above three methods in combination is to obtain the optimal adjustment strategy based on the sample data adjusted multiple times. Taking the adjustment of the repetition frequency of the photoacoustic laser light source 7 and the adjustment of the rotation speed of the rotary motor 31 as an example, it is assumed that the rotation speed of the rotary motor 31 is set to w0, and the repetition frequency of the photoacoustic laser light source 7 is n0 at this speed. When the instantaneous rotation speed of the head end of the endoscopic probe 1 is measured to be w0+w1 by the encoder 13, the signal synchronization unit 54 can be fed back to the laser control unit 51 to increase the repetition frequency of the photoacoustic laser light source 7 to n0+n1 / 2, thereby increasing the excitation frequency and sampling frequency of the endoscopic probe 1 at this time; and the signal synchronization unit 54 is fed back to the rotary motor control unit 53 to reduce the partial rotation speed of the rotary motor 31, thereby obtaining the optimal detection tissue 8 display image.

[0057] Those skilled in the art should know that three implementation methods using any one of the above three methods, three implementation methods using any two of the above three methods in combination, and an implementation method using the above three methods in combination should all be within the protection scope of this solution.

[0058] It is worth noting that Figure 2 and Figure 4 As shown, the balloon 2 includes a balloon portion 22 and a catheter 21, and the catheter 21 includes a front detection section 212 and a rear support section 211. The front detection section 212 is made of a transparent material for transmitting laser light, and the rear support section 211 is made of an opaque material. A circumferential grating structure 2111 is provided near the front detection section 212 for encoding light. The circumferential grating structure 2111 is a structure that is equally spaced and transparent. The rotation speed of the end of the endoscopic probe 1 close to the detection tissue 8 can be determined according to the interval between two light transmissions.

[0059] It is worth noting that the endoscopic probe 1 includes: a trigger 12, an encoder 13, a transducer 14, and an optical fiber 16, and the trigger 12, encoder 13, and transducer 14 are arranged at one end of the endoscopic probe 1 close to the external detection tissue 8, the trigger 12 is used to affect the external detection tissue 8 with the help of the first light beam, the encoder 13 is used to detect the rotation speed of one end of itself close to the external detection tissue 8 with the help of the first light beam, the transducer 14 is used to collect acoustic signals carrying information of the detection tissue 8, and the optical fiber 16 is used to transmit the first light beam.

[0060] It should be noted that the optical fiber 16 transmits the first light beam to the end of the endoscopic probe 1 close to the external detection tissue 8, the trigger 12 affects the external detection tissue 8 with the help of the first light beam, the transducer 14 collects the sound signal with the information of the detection tissue 8, and the encoder 13 is used to detect the rotation speed of its own end close to the external detection tissue 8 with the help of the first light beam.

[0061] It is worth noting that the endoscopic probe 1 also includes a second spectroscopic module 11 and a reflector 17. The second spectroscopic module 11 is used to decompose the first light beam into a third light beam and a fourth light beam, and transmit the third light beam to the trigger 12, and transmit the fourth light beam to the encoder 13 via reflection of the reflector 17. The third light beam is a trigger light that affects the external detection tissue 8, and the fourth light beam is the detection light of the encoder 13.

[0062] It should be noted that the third light beam is transmitted to the trigger 12 and is used as a trigger light to irradiate the detection tissue 8, so that the detection tissue 8 causes an instantaneous expansion effect due to the irradiation of the third light beam, thereby generating an ultrasonic signal. The fourth light beam serves as the detection light of the encoder 13 to irradiate the circular grating structure 2111 of the balloon 2, thereby determining the rotation speed of the end of the endoscopic probe 1 close to the detection tissue 8.

[0063] It is worth noting that the endoscopic probe 1 further includes a torque spring 15 , which is connected to the rotary coupling device 3 and is used to enable the rotary coupling device 3 to drive the endoscopic probe 1 to rotate.

[0064] It is worth noting that the first spectroscopic module 4 and the second spectroscopic module 11 are dichroic mirrors or beam splitters. When the first spectroscopic module 4 and the second spectroscopic module 11 are dichroic mirrors, the endoscopic probe 1 also includes an encoder light source 901, and the wavelength of light generated by the encoder light source 901 is different from the wavelength of the laser generated by the photoacoustic laser light source 7.

[0065] It should be noted that dichroic mirrors and beam splitters are both optical components used to control light in the optical path, such as Figure 5 As shown, the dichroic mirror can effectively reflect certain wavelengths of light and transmit other wavelengths of light, so an encoder light source 901 is required. The wavelength of the light generated by the encoder light source 901 is different from the wavelength of the laser generated by the photoacoustic laser light source 7, and the wavelength of the light generated by the encoder light source 901 meets the wavelength requirement of being reflected by the dichroic mirror, while the light generated by the photoacoustic laser light source 7 meets the wavelength requirement of being transmitted by the dichroic mirror, thereby achieving the purpose of beam splitting; the beam splitter does not distinguish light based on the wavelength of light, but divides the incident light into two parts according to a certain ratio, one part is reflected and the other part is transmitted. The dichroic mirror or beam splitter can be selected according to different application environments to achieve better imaging effects.

[0066] It should be noted that if Figure 3 As shown, when the first spectroscopic module 4 and the second spectroscopic module 11 are beam splitters, the light generated by the photoacoustic laser light source 7 is decomposed into a transmitted first light beam and a reflected second light beam through the first spectroscopic module 4, the first light beam is transmitted through the rotary coupling device 3 and the optical fiber 16, and then decomposed into a transmitted third light beam and a reflected fourth light beam through the second spectroscopic module 11, the third light beam is a trigger light that affects the external detection tissue 8, and the fourth light beam is used as the detection light of the encoder 13 to irradiate the detection tissue 8.

[0067] It should be noted that if Figure 5As shown, when the first spectroscopic module 4 and the second spectroscopic module 11 are dichroic mirrors, the light generated by the photoacoustic laser light source 7 is projected through the first spectroscopic module 4, and is transmitted through the rotary coupling device 3 and the optical fiber 16, and after being transmitted through the second spectroscopic module 11 and reflected by the reflector 17, it serves as a trigger light (third light beam) that affects the external detection tissue 8; the second light beam generated by the encoder light source 901 is reflected by the first spectroscopic module 4, and is transmitted through the rotary coupling device 3 and the optical fiber 16, and after being reflected by the second spectroscopic module 11, it serves as the detection light (fourth light beam) of the encoder 13 to irradiate the detection tissue 8.

[0068] It should be noted that the optical fiber 16 is a single-mode optical fiber 16 or a multi-mode optical fiber 16 .

[0069] It should be noted that single-mode optical fiber 16 and multi-mode optical fiber 16 are two different types of optical fibers 16, which have significant differences in structure, performance and application. First, the core diameter of single-mode optical fiber 16 is very small, only about 9 microns, which makes it only able to transmit light of one wavelength, with extremely low modal dispersion and high bandwidth, suitable for communications with long distance and high bandwidth requirements, such as long-distance telephone networks and data centers. However, the cost of single-mode optical fiber 16 is relatively high, and the requirements for light sources are more stringent, and laser light sources are usually required. In contrast, the core diameter of multi-mode optical fiber 16 is larger, usually 50 or 62.5 microns, which can allow multiple different wavelengths of light to be transmitted simultaneously. Therefore, although its bandwidth is limited, its cost is low, installation is simple, and the light source selection is wider, which is suitable for short-distance communications, such as local area networks and internal connections in data centers. Therefore, a single-mode optical fiber 16 or a multi-mode optical fiber 16 can be selected according to the dichroic mirror or beam splitter used. If a dichroic mirror is used, the optical fiber 16 corresponds to a multi-mode optical fiber 16, and if a beam splitter is used, the optical fiber 16 corresponds to a single-mode optical fiber 16.

[0070] In other embodiments of the present application, an endoscopic probe 1 is provided, which includes a spectroscopic module and an encoder 13. The spectroscopic module is used to decompose external light, and the encoder 13 is used to detect the rotation speed of one end of the endoscopic probe 1 close to the external detection tissue 8.

[0071] In the above-mentioned embodiment, a computer device is also provided, including a memory and a processor, wherein the memory stores a computer program, and when the processor executes the computer program, it can adjust the repetition frequency of the external photoacoustic laser light source 7, adjust the rotation speed of the external rotary motor 31, and adjust one or more of the acquired data splicing algorithms to adjust the image of the external detection tissue 8.

[0072] It should be noted that the computer program is flexible and adaptable, so that the execution steps can be adjusted according to different inputs and conditions, so as to adapt to the ever-changing needs and technical environment and maintain the advancement and practicality of the computer program. In addition, the architecture of the computer device allows the realization of multiple functions, so that the program in the memory can contain multiple functional modules, and the computer program can be executed by the processor to meet different application needs, thereby improving the function of the computer program and enhancing the integration of the computer device.

[0073] It should be noted that when a component is referred to as being "fixed to" or "disposed on" another component, it may be directly on the other component or there may also be a central component. When a component is considered to be "connected to" another component, it may be directly connected to the other component or there may be a central component at the same time. The terms "vertical", "horizontal", "upper", "lower", "left", "right" and similar expressions used in the specification of this application are for illustrative purposes only and do not represent the only implementation method.

[0074] In addition, the terms "first" and "second" are used only for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly indicating the number of indicated technical features. Thus, the features defined as "first" and "second" may explicitly or implicitly include at least one of the features. In the description of the present application, the meaning of "multiple" is at least two, such as two, three, etc., unless otherwise clearly and specifically defined. In addition, the terms "including" and "having" and any of their variations are intended to cover non-exclusive inclusions. For example, a process, method, device, product or equipment that includes a series of steps or units is not limited to the listed steps or units, but optionally also includes steps or units that are not listed, or optionally also includes other steps or units inherent to these processes, methods, products or equipment.

[0075] In the present application, unless otherwise clearly specified and limited, a first feature being “above” or “below” a second feature may mean that the first feature is directly in contact with the second feature, or the first feature and the second feature are indirectly in contact through an intermediate medium. Moreover, a first feature being “above”, “above” or “above” a second feature may mean that the first feature is directly above or obliquely above the second feature, or simply means that the first feature is higher in level than the second feature. A first feature being “below”, “below” or “below” a second feature may mean that the first feature is directly below or obliquely below the second feature, or simply means that the first feature is lower in level than the second feature.

[0076] Unless otherwise defined, all technical and scientific terms used in the specification of this application have the same meaning as those commonly understood by those skilled in the art to which this application belongs. The terms used in the specification of this application are only for the purpose of describing specific embodiments and are not intended to limit this application. The term "and / or" used in the specification of this application includes any and all combinations of one or more related listed items.

[0077] The technical features of the above embodiments can be combined without changing the basic principles of the present application. To make the description concise, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0078] The above embodiments only express several implementation methods of the present application, and the descriptions thereof are relatively specific and detailed, but they cannot be understood as limiting the scope of the patent application. It should be pointed out that, for a person of ordinary skill in the art, several variations and improvements can be made without departing from the concept of the present application, and these all belong to the protection scope of the present application. Therefore, the scope of patent protection of the present application shall be subject to the attached claims.

Claims

1. A photoacoustic endoscopy component, characterized in that: The photoacoustic endoscopy assembly comprises: An endoscopic probe, a balloon, a rotary coupling device, a first light splitting module, a control unit, a display device, and a photoacoustic laser light source; One end of the photoacoustic laser light source is connected to the control unit, and the other end of the photoacoustic laser light source is connected to one end of the first light splitting module; The other end of the first light splitting module is connected to the first end of the rotary coupling device; The second end of the rotary coupling device is connected to the control unit, and the third end of the rotary coupling device is connected to the endoscope probe; The endoscopic probe is arranged in the balloon, and the endoscopic probe can rotate inside the balloon driven by the rotary coupling device, and is used to influence the external detection tissue by means of the first light beam generated by the photoacoustic laser light source, so as to collect the acoustic signal with the detection tissue information, and transmit it to the control unit via the rotary coupling device, and the endoscopic probe is also used to detect the rotation speed of one end of the endoscopic probe close to the external detection tissue by using the first light beam, and transmit the optical signal with the rotation speed information to the control unit via the rotary coupling device and the first light splitting module in sequence; The balloon has a hollow space; The control unit is connected to the display device and is used to control the display device to display the image of the detected tissue according to the acoustic signal, and the control unit is also used to adjust one or more of the photoacoustic laser light source, the rotary coupling device and the display device according to the optical signal; The display device is used to display the image of the detected tissue.

2. The photoacoustic endoscopy assembly according to claim 1, characterized in that: The rotary coupling device includes a rotary motor and a coupler. The rotary motor is connected to the coupler. The rotary motor is used to drive the endoscope probe to rotate. The coupler is used to transmit the signal through the rotary coupling device.

3. The photoacoustic endoscopy assembly according to claim 2, characterized in that: The control unit adjusts the image of the detected tissue by adjusting one or more of the repetition frequency of the photoacoustic laser light source, the rotation speed of the rotary motor, and the acquisition data splicing algorithm.

4. The photoacoustic endoscopy assembly according to claim 1, characterized in that: The balloon includes a balloon portion and a catheter, the catheter includes a front detection section and a rear support section, the front detection section is made of a transparent material, the rear support section is made of an opaque material, and a circumferential grating structure is arranged on the catheter near the front detection section.

5. The photoacoustic endoscopy assembly according to claim 1, characterized in that: The endoscopic probe includes: a trigger, an encoder, a transducer, and an optical fiber, and the trigger, encoder, and transducer are arranged at one end of the endoscopic probe close to the external detection tissue, the trigger is used to influence the external detection tissue with the help of the first light beam, the encoder is used to detect the rotation speed of one end of itself close to the external detection tissue with the help of the first light beam, the transducer is used to collect acoustic signals carrying detection tissue information, and the optical fiber is used to transmit the first light beam.

6. The photoacoustic endoscopy assembly according to claim 5, characterized in that: The endoscopic probe also includes a second spectroscopic module and a reflector. The second spectroscopic module is used to decompose the first light beam into a third light beam and a fourth light beam, and transmit the third light beam to the trigger, and transmit the fourth light beam to the encoder via reflection of the reflector. The third light beam is a trigger light that affects the external detection tissue, and the fourth light beam is a detection light of the encoder.

7. The photoacoustic endoscopy assembly according to claim 6, characterized in that: The first spectroscopic module and the second spectroscopic module are dichroic mirrors. The photoacoustic endoscopy assembly further includes an encoder light source. The wavelength of light generated by the encoder light source is different from the wavelength of the laser generated by the photoacoustic laser light source.

8. The photoacoustic endoscopy assembly according to claim 6, characterized in that: The first light splitting module and the second light splitting module are beam splitters.

9. An endoscope probe, applied to the photoacoustic endoscope assembly as claimed in any one of claims 1 to 8, characterized in that: The endoscope probe comprises a spectroscopic module and an encoder. The spectroscopic module is used to decompose external light, and the encoder is used to detect the rotation speed of the end of the endoscope probe close to the external detection tissue.

10. A computer device, characterized in that: It comprises a memory and a processor, wherein the memory stores a computer program, and when the processor executes the computer program, it realizes one or more of adjusting the repetition frequency of an external photoacoustic laser light source, adjusting the rotation speed of an external rotary motor, and adjusting the acquisition data splicing algorithm as described in claim 3 to adjust the image of the external detection tissue.

Images