OCT optical catheter and OCT flexible oral cavity endoscopic imaging system

Abstract

The invention relates to an OCT (optical coherence tomography) optical catheter and an OCT flexible oral cavity endoscopic imaging system, and the OCT optical catheter comprises a controllable flexible structure and an imaging automatic focusing structure; the controllable flexible structure comprises an optical fiber, a transparent tube sheath wrapping the outer layer of the optical fiber, and a controllable shaft arranged on the outer layer of the protective tube sheath; the controllable shaft is connected with the driver; the imaging automatic focusing structure comprises a collimator arranged at the end of the optical fiber, a liquid lens arranged at the front end of the collimator, a doublet lens arranged at the front end of the liquid lens and an MEMS reflector arranged at the front end of the doublet lens. The collimator, the liquid lens, the doublet lens and the MEMS reflector are sequentially fixed in the shell. Compared with the prior art, the device is compact in structure and can go deep into some positions difficult to detect, meanwhile, automatic focusing of oral cavity internal imaging is achieved, the imaging speed and range, the spatial resolution and the non-contact tomography are superior to those of an existing oral cavity detection technology, and structural characteristics of tiny tissue in the oral cavity can be distinguished more clearly.

Description

Technical Field

[0001] The invention relates to the field of biomedical optical technology, and in particular to an OCT optical catheter and an OCT flexible oral intraoral imaging system. Background Art

[0002] In recent years, the rapid development of optical coherence tomography (OCT) technology has provided favorable technical support for the detection of early oral diseases. Optical coherence tomography (OCT) is a high-resolution imaging technology that is usually used to observe the internal structure of biological tissues non-invasively and in real time. It is based on the principle of light interference and uses the interference between light beams and different tissues in the sample to generate high-definition tomographic images. OCT has the following characteristics: high resolution, non-invasive, real-time imaging, multimodal imaging, etc. It is widely used in many fields such as ophthalmology, dermatology, dentistry, internal medicine, and surgery.

[0003] Since 2005, the development of OCT oral detection technology has become increasingly mature. From the earliest OCT images that can image oral mucosa to the current microscopic characteristic structures of healthy and damaged gum tissue and teeth, the OCT oral detection technology can be clearly distinguished, which shows the strong potential of oral OCT technology in clinical "optical biopsy". At present, the international oral OCT system is in the clinical trial stage, while there is no domestic equipment for oral OCT detection system. The development of OCT oral detection system has great research and development and social benefits for the diagnosis of early oral diseases, asymptomatic oral cancer and squamous cell carcinoma.

[0004] At present, most of the optical catheters used for oral OCT endoscopic imaging use a 4f system lens group, and the catheters are mostly rigid and lack automatic focusing function, which will lead to many limitations. First, the rigid probe may cause discomfort in the mouth, especially for some patients with oral sensitivity, which may lead to a bad experience. Secondly, the rigid probe has a large shape and size, which will limit the scanning range and make it difficult to effectively image the deeper or narrow areas inside the mouth. In addition, since the depth and morphology of the internal structure of the oral cavity often vary greatly, if automatic focusing cannot be achieved, it is very easy to cause unstable imaging quality, affecting the accuracy of diagnosis and analysis. In addition, if the focus needs to be adjusted manually, it will increase the cumbersomeness and time cost of the operation, especially in real-time imaging or clinical diagnosis, which may affect the doctor's judgment of the patient's condition. Moreover, the environmental conditions inside the oral cavity may be more complex, such as saliva, saliva, gas and other factors may affect the optical path, and the inability to automatically focus will make the system more susceptible to interference from these factors. Due to the inability to automatically focus, the scanning range will also be limited, and it is impossible to perform more detailed imaging of the deeper or local specific areas inside the oral cavity. Summary of the invention

[0005] The purpose of the present invention is to provide an OCT optical catheter and an OCT flexible intraoral imaging system in order to overcome the defects of the above-mentioned prior art. The system has a compact structure and can penetrate into some difficult-to-detect locations. At the same time, it can realize automatic focusing of intraoral imaging. The imaging speed and range, spatial resolution and non-contact tomography are superior to the current oral detection technology. It will be able to more clearly distinguish the structural characteristics of tiny tissues in the oral cavity and provide better technical support for the clinical detection of oral diseases.

[0006] The purpose of the present invention can be achieved by the following technical solutions:

[0007] The present invention provides an OCT optical catheter, comprising a controllable flexible structure and an imaging automatic focusing structure;

[0008] The controllable flexible structure comprises: an optical fiber, a transparent sheath wrapped around the outer layer of the optical fiber, and a controllable shaft arranged on the outer layer of the protective sheath; the controllable shaft is connected to a driver; the driver pulls the controllable shaft in an antagonistic manner to change the bending angle, and the movement of the oral probe is controlled by changing the bending angle;

[0009] The imaging automatic focusing structure comprises: a collimator arranged at the end of the optical fiber, a liquid lens arranged at the front end of the collimator, a double-cemented lens arranged at the front end of the liquid lens, and a MEMS reflector arranged at the front end of the double-cemented lens. The collimator, the liquid lens, the double-cemented lens, and the MEMS reflector are fixed inside the housing in sequence; a cable is arranged on the side of the controllable shaft to connect the liquid lens and the MEMS reflector structure. The liquid lens is driven by dielectric force, and the MEMS reflector is driven by electric heat.

[0010] Furthermore, the driver is enclosed inside with an electric bending actuator, the electric bending actuator is provided with a pulley and a motor, the motor and the pulley are connected by a belt, a cable pulling trolley is provided on the belt, and the antagonistic cable is connected to the cable pulling trolley; the proximal end of the controllable shaft is equipped with an electric bending actuator enclosed in the driver.

[0011] Furthermore, the front end bendable portion of the steerable shaft is composed of cylindrical vertebrae, and antagonistic cables are inserted on both sides of the cylindrical vertebrae. The bending movement within the range of -60° to 90° is driven by two antagonistic cables enclosed in the steerable shaft.

[0012] Furthermore, the vertebrae are connected by snap fasteners.

[0013] Furthermore, a transparent protective window is provided on the housing. The transparent protective window prevents the formation of water mist on the surface of the oral probe due to temperature changes, which affects the imaging quality, and ensures the clarity and transparency of the imaging; at the same time, it can protect the optical elements in the oral probe from the influence of the oral environment, such as saliva or bacteria, etc., prolong the service life of the optical elements, and maintain the stability of the imaging quality.

[0014] Furthermore, the optical fiber is connected to the collimator via an FC / APC connector.

[0015] Furthermore, the MEMS reflector is connected to a PCB board, and welding wires are welded on the back of the PCB board. The welding wires are five copper wires to form a connection with five pads on the front of the PCB board; the PCB board is connected to an external power supply and is provided with a plurality of pins, and the MEMS chip is connected to the corresponding pins.

[0016] The PCB board is bonded to the top slot and wire-bonded to the MEMS chip. Five gold wires are soldered to the pads on the MEMS chip, and finally the MEMS chip is placed and bonded in the cavity designed for it. The MEMS reflector uses the electrothermal effect to adjust the shape of the mirror surface. By applying different intensities of current to different parts of the reflector, the mirror surface is locally heated, resulting in a slight thermal expansion or thermal strain effect, thereby changing the curvature radius or tilt angle of the reflector, and then adjusting the direction of the reflected light beam and the focusing performance.

[0017] The present invention also provides an OCT flexible intraoral imaging system, comprising: an OCT optical catheter, a driver, a distance sensor, a volume scanning actuator, a control panel, a wavelength division multiplexer, and a CMOS camera;

[0018] The OCT optical catheter is connected to a driver, the driver is connected to a volume scanning actuator, the volume scanning actuator is connected to a control panel, the control panel and the distance sensor are both connected to a computer, the control panel receives an electrical signal from the computer and transmits it to the volume scanning actuator, the volume scanning actuator controls the movement of the driver so that the imaging head of the oral endoscope performs a scanning movement inside the oral cavity to obtain imaging data at different angles and depths inside the oral cavity; the distance sensor receives reflected light carrying tissue information, and measures the time for near-infrared light emitted by a light source to be emitted from the distance sensor to the target object and reflected back to the distance sensor, then calculates the distance between the target object and the sensor based on the speed of light and time, and converts the optical signal into an electrical signal; the volume scanning actuator is composed of a rotary joint and a linear translation platform.

[0019] The computer controls the voltage of the liquid lens through the control panel to adjust the curvature of the liquid lens, changes the interface shape between the two liquids of the liquid lens to change the curvature radius of the liquid lens, and realizes the focusing function according to different working distances; at the same time, the voltage of the MEMS reflector is changed to adjust the deflection angle to change the working distance of the system;

[0020] The wavelength division multiplexer is connected to the CMOS camera and the OCT optical catheter.

[0021] Furthermore, the wavelength division multiplexer is connected to the OCT optical catheter via a multimode optical fiber, and 1310 nm infrared light and visible light can pass through the multimode optical fiber at the same time. The visible light locates the oral tissue to be detected and displays it in real time.

[0022] Furthermore, the OCT optical catheter can simultaneously pass infrared light and visible light, and the two different wavelengths of light are focused on the sample to be tested, the reflected light returns along the original path, the visible light returns to the CMOS camera through the wavelength division multiplexer for imaging, and the infrared light interferes with the return light from the reference arm and the photoelectric balance detector receives the signal. Finally, two images are formed on the computer display screen, namely the OCT image and the CMOS camera image.

[0023] The imaging method of the present invention comprises the following steps:

[0024] In the first step, the laser light source inputs incident light through the optical fiber, enters the housing, passes through the collimator and liquid lens in sequence, and is focused by the double-cemented lens while reducing axial chromatic aberration. The focused light beam is totally reflected on the inclined surface of the MEMS reflector, and then emerges through the transparent protective window to irradiate the sample tissue.

[0025] In the second step, the reflected light from the sample tissue returns along the original optical path and enters the distance sensor. The distance sensor obtains the actual required working distance of the endoscope based on the intensity of the reflected light signal and other optical characteristics, and the distance sensor converts the optical signal into an electrical distance signal.

[0026] In the third step, the obtained electrical signal is transmitted to the control panel through the computer. The control panel adjusts the voltage of the liquid lens to achieve the change of the curvature of the liquid lens. The change of curvature means that the focal length changes accordingly to achieve self-focusing. At the same time, the voltage on the MEMS reflector is changed to control the change of the deflection focal length of the MEMS reflector, thereby changing the working distance of the oral intraocular camera.

[0027] In the fourth step, the laser is emitted again to irradiate the sample tissue, and the reflected light returns to the distance sensor along the original optical path. The distance sensor transmits the electrical signal to the computer, and the computer calculates whether the lateral resolution of the image reaches the set criterion. If it does, the voltage adjustment of the liquid lens and the MEMS mirror is stopped; if it does not reach the set criterion, the second and third steps are repeated until it is reached.

[0028] The optical path principle of the reference arm part is consistent with that of the general OCT system reference arm. The optical path principle of the sample arm part is as follows: the light emitted by the visible light source passes through the optical fiber circulator to reach the wavelength division multiplexer, and is combined with the light of the swept frequency light source to be transmitted in an optical fiber, and is incident on the sample through the sample arm. The light reflected from the sample returns along the original path and reaches the wavelength division multiplexer, and the visible light and near-infrared light are re-carried separately. The visible light enters the CMOS camera through the circulator, and the near-infrared light interferes with the return light of the reference arm through the circulator.

[0029] Compared with the prior art, the present invention has the following advantages:

[0030] (1) Compared with the traditional rigid oral imaging system, the present invention can bend and adapt to different shapes and structures in the oral cavity, can better enter the deep tissue of the oral cavity, and improve the comprehensiveness and depth of imaging;

[0031] (2) Due to the characteristics of the flexible probe, it causes less stimulation and damage to the tissue when inserted into the oral cavity, reducing the risk of possible damage to the oral tissue;

[0032] (3) The adjustable focus probe of the present invention can adapt to oral tissue structures of different depths and shapes by adjusting the focal length, ensuring that the probe is always in the optimal focal length position, thereby obtaining clearer and more accurate imaging results and reducing the occurrence of blur and out-of-focus phenomena;

[0033] (4) The combination of MEMS mirrors and liquid lenses can achieve dynamic focusing and continuous zooming functions. MEMS mirrors provide fast response and precise control, and liquid lenses can achieve continuous focal length adjustment. Together, they can achieve rapid switching of focus and zoom during oral examinations, allowing for clearer observation of details inside the oral cavity. At the same time, the inside of the oral cavity can be observed and imaged at different angles, directions, and focal lengths according to actual needs, improving the flexibility and comprehensiveness of oral examinations.

[0034] (5) The lateral resolution of this system is about 10 microns, which can more clearly distinguish the tiny structures in the sample tissue. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] Figure 1 This is an imaging flow chart of Example 1;

[0036] Figure 2 is a schematic diagram of an optical OCT catheter in the present invention;

[0037] Figure 3 MEMS mirror structure diagram

[0038] Figure 4 It is a schematic diagram of the drive structure;

[0039] Figure 5 Schematic diagram of the structure of the oral OCT imaging system.

[0040] Figure numerals: 1-optical fiber, 2-collimator, 3-liquid lens, 4-double cemented lens, 5-MEMS mirror, 6-transparent protective window, 7-housing, 8-antagonistic cable, 9-steerable axis, 10-vertebra, 11-cable, 12-PCB board, 13-bonding wire, 15-pulley, 16-cable trolley, 17-motor, 18-belt, 19-MEMS chip, 20-pin, 21-distance sensor, 22-volume scanning actuator, 23-control panel, 24-wavelength division multiplexer, 25-CMOS camera, 26-multimode optical fiber. DETAILED DESCRIPTION

[0041] The present invention is described in detail below in conjunction with the accompanying drawings and specific embodiments. Component models, material names, connection structures, control methods, algorithms and other features not clearly described in this technical solution are all considered to be common technical features disclosed in the prior art.

[0042] It should be noted that when a component is considered to be "connected" to another component, it can be directly connected to another component, or connected to another component through an intermediate component. The "connection" in the following embodiments should be understood as "electrical connection", "communication connection", etc. if the connected components, circuits, modules, units, etc. have electrical signals or data transmission between each other.

[0043] Example 1

[0044] This embodiment provides an OCT optical catheter, such as Figure 2 , 3 , as shown in 4, including a controllable flexible structure and an imaging automatic focusing structure;

[0045] The controllable flexible structure comprises: an optical fiber 1, a transparent sheath wrapped around the outer layer of the optical fiber 1, and a controllable shaft 9 provided on the outer layer of the protective sheath; the controllable shaft 9 is connected to a driver; the driver pulls the controllable shaft 9 in an antagonistic manner to change the bending angle, and controls the movement of the oral probe by changing the bending angle;

[0046] The imaging automatic focusing structure comprises: a collimator 2 arranged at the end of an optical fiber 1, a liquid lens 3 arranged at the front end of the collimator 2, a double-cemented lens 4 arranged at the front end of the liquid lens 3, and a MEMS reflector 5 arranged at the front end of the double-cemented lens 4. The collimator 2, the liquid lens 3, the double-cemented lens 4, and the MEMS reflector 5 are fixed in sequence inside a housing 7; a cable 11 is provided on the side of the manipulable shaft 9 to connect the liquid lens 3 and the MEMS reflector 5 structure. The liquid lens 3 is driven by dielectric force, and the MEMS reflector 5 is driven by electrothermal force.

[0047] In a specific embodiment, the driver is enclosed inside with an electric bending actuator, the electric bending actuator is provided with a pulley 15 and a motor 17, the motor 17 and the pulley 15 are connected by a belt 18, a cable pulling trolley 16 is provided on the belt 18, and the antagonistic cable 8 is connected to the cable pulling trolley 16; the proximal end of the controllable shaft 9 is equipped with an electric bending actuator enclosed in the driver.

[0048] In a specific embodiment, the front end bendable portion of the steerable shaft 9 is composed of a cylindrical vertebra 10, and antagonist cables 8 are inserted on both sides of the cylindrical vertebra 10. The bending movement within the range of -60° to 90° is driven by two antagonist cables 8 enclosed in the steerable shaft 9.

[0049] In a specific embodiment, the vertebrae 10 are connected by snap-fit.

[0050] In a specific embodiment, a transparent protective window 6 is provided on the housing 7. The transparent protective window 6 prevents the surface of the oral probe from forming water mist due to temperature changes, which affects the imaging quality, and ensures the clarity and transparency of the imaging; at the same time, it can protect the optical elements in the oral probe from being affected by the oral environment, such as saliva or bacteria, etc., prolonging the service life of the optical elements and maintaining the stability of the imaging quality.

[0051] In a specific implementation, the optical fiber 1 is connected to the collimator 2 via an FC / APC connector.

[0052] In a specific embodiment, the MEMS reflector 5 is connected to a PCB board 12, and welding wires 13 are welded on the back of the PCB board 12. The welding wires 13 are five copper wires to form a connection with five pads on the front of the PCB board 12; the PCB board 12 is connected to an external power supply and is provided with a plurality of pins 20, and the MEMS chip 19 is connected to the corresponding pins 20.

[0053] The PCB board 12 is bonded to the top slot and wire-bonded to the MEMS chip 19. Five gold wires are soldered to the pads on the MEMS chip 19, and finally the MEMS chip 19 is placed and bonded in the cavity designed for it. The MEMS reflector 5 uses the electrothermal effect to adjust the shape of the mirror surface. By applying currents of different intensities to different parts of the reflector, the mirror surface is locally heated, resulting in a slight thermal expansion or thermal strain effect, thereby changing the curvature radius or tilt angle of the reflector, and then adjusting the direction of the reflected light beam and the focusing performance.

[0054] like Figure 5 As shown, this embodiment also provides an OCT flexible intraoral imaging system, characterized in that it includes: an OCT optical catheter, a driver, a distance sensor 21, a volume scanning actuator 22, a control panel 23, a wavelength division multiplexer 24, and a CMOS camera 25;

[0055] The OCT optical catheter is connected to a driver, the driver is connected to a volume scanning actuator 22, the volume scanning actuator 22 is connected to a control panel 23, the control panel 23 and the distance sensor 21 are both connected to a computer, the control panel 23 receives an electrical signal from the computer and transmits it to the volume scanning actuator 22, the volume scanning actuator 22 controls the movement of the driver so that the imaging head of the oral endoscope performs a scanning movement inside the oral cavity to obtain imaging data at different angles and depths inside the oral cavity; the distance sensor 21 receives reflected light carrying tissue information, and measures the time for the near-infrared light emitted by the light source to be emitted from the distance sensor 21 to the target object and then reflected back to the distance sensor 21, and then calculates the distance between the target object and the sensor according to the speed of light and time, and converts the optical signal into an electrical signal; the volume scanning actuator 22 is composed of a rotary joint and a linear translation platform.

[0056] The computer controls the voltage of the liquid lens 3 through the control panel 23 to adjust the curvature of the liquid lens 3, changes the interface shape between the two liquids of the liquid lens 3 to change the curvature radius of the liquid lens 3, and realizes the focusing function according to different working distances; at the same time, the voltage of the MEMS reflector 5 is changed to adjust the deflection angle to change the system working distance;

[0057] The wavelength division multiplexer 24 is connected to the CMOS camera 25 and the OCT optical catheter.

[0058] In a specific embodiment, the wavelength division multiplexer 24 is connected to the OCT optical catheter via a multimode optical fiber 26, and the multimode optical fiber 26 can simultaneously pass 1310nm infrared light and visible light. The visible light locates the oral tissue to be detected and displays it in real time.

[0059] In a specific embodiment, the OCT optical catheter can pass infrared light and visible light at the same time. The two different wavelengths of light are focused on the sample to be tested, the reflected light returns along the original path, the visible light returns to the CMOS camera 25 through the wavelength division multiplexer 24 for imaging, and the infrared light interferes with the returned light from the reference arm and the signal is received by the photoelectric balance detector. Finally, two images are formed on the display screen of the computer, namely the OCT image and the CMOS camera image.

[0060] The imaging method of the present invention, such as Figure 1 , Figure 5 As shown, the following steps are included:

[0061] In the first step, the laser light source inputs incident light through the optical fiber 1, enters the housing 7, passes through the collimator 2 and the liquid lens 3 in sequence, and is focused by the double cemented lens 4 while reducing the axial chromatic aberration. The focused light beam is totally reflected on the inclined surface of the MEMS reflector 5, and is emitted through the transparent protective window 6 to irradiate the sample tissue;

[0062] In the second step, the reflected light of the sample tissue returns along the original optical path and enters the distance sensor 21. The distance sensor 21 obtains the actual required working distance of the endoscope according to the intensity of the reflected light signal and other optical characteristics, and the distance sensor 21 converts the optical signal into an electrical distance signal;

[0063] In the third step, the obtained electrical signal is transmitted to the control panel 23 through the computer. The control panel 23 adjusts the voltage of the liquid lens 3 to achieve the change of the curvature of the liquid lens 3. The change of curvature means that the focal length changes accordingly to achieve self-focusing. At the same time, the voltage on the MEMS reflector 5 is changed to control the change of the deflection focal length of the MEMS reflector 5, thereby changing the working distance of the oral endoscope;

[0064] In the fourth step, the laser is emitted again to irradiate the sample tissue, and the reflected light returns to the distance sensor 21 along the original optical path. The distance sensor 21 transmits the electrical signal to the computer, and the computer calculates whether the lateral resolution of the image reaches the set criterion. If it reaches it, the voltage adjustment of the liquid lens 3 and the MEMS mirror 5 is stopped; if it does not reach the set criterion, the second and third steps are repeated until it reaches it.

[0065] The optical path principle of the reference arm part is consistent with that of the general OCT system reference arm. The optical path principle of the sample arm part is as follows: the light emitted by the visible light source passes through the optical fiber circulator to reach the wavelength division multiplexer 24, is combined with the light of the swept frequency light source to be transmitted in an optical fiber 1, is incident on the sample through the sample arm, and the light reflected from the sample returns through the original path to reach the wavelength division multiplexer 24, and the visible light and near-infrared light are re-carried separately, wherein the visible light enters the CMOS camera 25 through the circulator, and the near-infrared light interferes with the return light of the reference arm through the circulator.

[0066] Components not described in detail in this embodiment are all existing components that can be purchased through public channels.

[0067] The above description of the embodiments is to facilitate the understanding and use of the invention by those skilled in the art. It is obvious that those skilled in the art can easily make various modifications to these embodiments and apply the general principles described herein to other embodiments without creative work. Therefore, the present invention is not limited to the above embodiments, and improvements and modifications made by those skilled in the art based on the disclosure of the present invention without departing from the scope of the present invention should be within the scope of protection of the present invention.

Claims

1. An OCT optical catheter, characterized in that: Including controllable flexible structure and imaging automatic focusing structure; The controllable flexible structure comprises: an optical fiber (1), a transparent sheath wrapped around the outer layer of the optical fiber (1), and a controllable shaft (9) arranged on the outer layer of the protective sheath; the controllable shaft (9) is connected to a driver; the driver pulls the controllable shaft (9) in an antagonistic manner to change the bending angle, and the movement of the oral probe is controlled by changing the bending angle; The imaging automatic focusing structure comprises: a collimator (2) arranged at the end of an optical fiber (1), a liquid lens (3) arranged at the front end of the collimator (2), a double-cemented lens (4) arranged at the front end of the liquid lens (3), and a MEMS reflector (5) arranged at the front end of the double-cemented lens (4); the collimator (2), the liquid lens (3), the double-cemented lens (4), and the MEMS reflector (5) are fixed in sequence inside a housing (7); and a cable (11) is provided on the side of the controllable shaft (9) to connect the liquid lens (3) and the MEMS reflector (5) structure.

2. An OCT optical catheter according to claim 1, characterized in that: The driver is enclosed with an electric bending actuator, which is provided with a pulley (15) and a motor (17). The motor (17) and the pulley (15) are connected by a belt (18). A cable-pulling trolley (16) is provided on the belt (18), and an antagonistic cable (8) is connected to the cable-pulling trolley (16). The proximal end of the controllable shaft (9) is provided with the electric bending actuator enclosed in the driver.

3. An OCT optical catheter according to claim 1, characterized in that: The front end bendable part of the steerable shaft (9) is composed of vertebrae (10), and antagonistic cables (8) are inserted on both sides of the vertebrae (10). The bending movement is driven by two antagonistic cables (8) enclosed in the steerable shaft (9).

4. An OCT optical catheter according to claim 3, characterized in that: The vertebrae (10) are connected via buckles.

5. The OCT optical catheter according to claim 1, characterized in that: The housing (7) is provided with a transparent protection window (6).

6. The OCT optical catheter according to claim 1, characterized in that: The optical fiber (1) and the collimator (2) are connected via an FC / APC connector.

7. The OCT optical catheter according to claim 1, characterized in that: The MEMS reflector (5) is connected to a PCB board (12); a welding wire (13) is welded on the back of the PCB board (12); the welding wire (13) is five copper wires, so as to form a connection with five welding pads on the front of the PCB board (12); the PCB board (12) is connected to an external power supply and is provided with a plurality of pins (20); and the MEMS chip (19) is connected to corresponding pins (20).

8. An OCT flexible intraoral imaging system, characterized in that: include: OCT optical catheter, driver, distance sensor (21), volume scanning actuator (22), control panel (23), wavelength division multiplexer (24), CMOS camera (25); The OCT optical catheter is connected to a driver, the driver is connected to a volume scanning actuator (22), the volume scanning actuator (22) is connected to a control panel (23), the control panel (23) and the distance sensor (21) are both connected to a computer, the control panel (23) receives an electrical signal from the computer and transmits it to the volume scanning actuator (22), the volume scanning actuator (22) controls the movement of the driver so that the imaging head of the oral intrascope performs a scanning movement inside the oral cavity to obtain imaging data at different angles and depths inside the oral cavity; the distance sensor (21) receives reflected light carrying tissue information, measures the time taken for near-infrared light emitted by a light source to be emitted from the distance sensor (21) to the target object and then reflected back to the distance sensor (21), and converts the optical signal into an electrical signal; The computer controls the voltage of the liquid lens (3) through the control panel (23) to adjust the curvature of the liquid lens (3), and at the same time changes the voltage of the MEMS reflector (5) to adjust the deflection angle so as to change the working distance of the system; The wavelength division multiplexer (24) is connected to the CMOS camera (25) and the OCT optical catheter.

9. The OCT flexible intraoral imaging system according to claim 8, characterized in that: The wavelength division multiplexer (24) is connected to the OCT optical catheter via a multimode optical fiber (26), and the multimode optical fiber (26) can simultaneously pass 1310nm infrared light and visible light, and the visible light locates the oral tissue to be detected and displays it in real time.

10. The OCT flexible intraoral imaging system according to claim 8, characterized in that: The OCT optical catheter can pass infrared light and visible light at the same time. The two different wavelengths of light are focused on the sample to be tested, the reflected light returns along the original path, the visible light returns to the CMOS camera (25) through the wavelength division multiplexer (24) for imaging, and the infrared light interferes with the returned light from the reference arm and the signal is received by the photoelectric balance detector.

Images