Detection device for photoacoustic imaging, endoscope processing device and imaging system

Abstract

The present invention discloses a detection device for photoacoustic imaging. A light guiding part guides a first laser and a second laser to propagate from the proximal end to the distal end, and guides the first laser to be emitted from the distal end of the light guiding part to the part to be measured, so that ultrasonic waves are generated at the part to be measured based on the action of the first laser. A photoacoustic modulation part is arranged at the distal end of the light guiding part. The photoacoustic modulation part is subject to the ultrasonic waves to modulate the second laser, and enables the modulated second laser to return along the light guiding part. An imaging result of the part to be measured can be obtained according to the modulated second laser. The detection device for photoacoustic imaging of the present invention can at least avoid using an ultrasonic transducer for emitting ultrasonic waves to the part to be measured and an ultrasonic transducer for receiving the ultrasonic waves reflected back by the part to be measured, can reduce the number of components used, and can reduce the diameter of the detection device. The present invention also discloses an endoscope processing device and an endoscope imaging system.

Description

Technical Field

[0001] The present invention relates to the field of photoacoustic imaging technology, and in particular to a detection device for photoacoustic imaging. The present invention also relates to an endoscope processing device and an endoscope imaging system. Background Art

[0002] Photoacoustic imaging is a newly emerging biomedical imaging technology in the past 20 years. In the past 10 years, it has begun to develop towards endoscopic imaging, and various forms of endoscopic small probes based on photoacoustic imaging have emerged.

[0003] Among them, the mechanical rotation scanning endoscope based on a single-element ultrasonic transducer is a relatively common technical form. In this type of small probe, ultrasonic waves are emitted to the biological tissue at the measured part, and the ultrasonic waves reflected back by the biological tissue are received. The single-element ultrasonic transducer converts the received ultrasonic waves into electrical signals and transmits them to the signal acquisition and processing device, and then image reconstruction is performed according to the acquired signals to obtain the imaging result of the measured part.

[0004] However, this type of probe contains many components, and at least includes an ultrasonic transducer for generating ultrasonic waves and an ultrasonic transducer for receiving ultrasonic echoes, which makes the probe diameter larger and not applicable to parts with a smaller internal space. Summary of the Invention

[0005] The object of the present invention is to provide a detection device for photoacoustic imaging, which can reduce the number of components used and can reduce the diameter of the detection device. The present invention also provides an endoscope processing device and an endoscope imaging system.

[0006] To achieve the above object, the present invention provides the following technical solutions:

[0007] A detection device for photoacoustic imaging includes a light guiding part, and the light guiding part is used to guide the first laser and the second laser to propagate from the proximal end to the distal end, so that the first laser is emitted from the distal end of the light guiding part to the measured part, and ultrasonic waves are generated in the measured part based on the action of the first laser;

[0008] A photoacoustic modulation part is arranged at the distal end of the light guiding part, and the photoacoustic modulation part is modulated by the ultrasonic waves to modulate the second laser, and the modulated second laser returns to the proximal end through the light guiding part.

[0009] Optionally, the photoacoustic modulation part is used to reflect back the light with the same wavelength as its own working wavelength, and the photoacoustic modulation part deforms under the action of the ultrasonic waves, so that the working wavelength of the photoacoustic modulation part changes.

[0010] Optionally, the photoacoustic modulation part includes a Bragg grating.

[0011] Optionally, the photoacoustic modulation unit is disposed inside the light guiding unit.

[0012] Optionally, the distal end face of the light guiding unit is an inclined surface, so that the first laser is emitted laterally of the light guiding unit.

[0013] Optionally, a reflection element is further included, which is configured to reflect the first laser emitted from the light guiding unit, so that the first laser is emitted toward the measured part.

[0014] Optionally, the distal end face of the light guiding unit is a flat surface.

[0015] Optionally, the detection device further includes a driving and conducting part, which is coated on the light guiding unit and at least exposes the emission area of the first laser and the photoacoustic modulation unit. The driving and conducting part is relatively stationary with respect to the light guiding unit and is configured to transmit a rotational torque.

[0016] Optionally, the detection device further includes a smooth ring connected to the light guiding unit.

[0017] Optionally, a housing is further included, and the light guiding unit is disposed inside the housing.

[0018] Optionally, a driving device is further included, which is configured to drive the light guiding unit to rotate and / or move axially.

[0019] The present invention further provides:

[0020] An endoscope processing device, which is connected to the detection device for photoacoustic imaging, includes a first light source assembly, a second light source assembly, a light guiding assembly, and an imaging assembly. The first light source assembly is configured to emit a first laser, and the second light source assembly is configured to emit a tunable second laser;

[0021] The light guiding assembly conducts the first laser and the second laser to the detection device, and conducts the modulated second laser returned by the detection device to the imaging assembly;

[0022] The imaging assembly is configured to perform imaging based on the modulated second laser returned by the detection device.

[0023] Optionally, during the detection process, the wavelength of the second laser emitted by the second light source assembly continuously changes.

[0024] Optionally, the absolute value of the difference between the wavelength of the first laser and the working wavelength of the detection device is greater than or equal to a preset value.

[0025] Optionally, the light guiding component includes a beam combiner and a first optical fiber. The beam combiner is configured to combine the optical fiber transmitting the first laser and the optical fiber transmitting the second laser into the first optical fiber, and through the first optical fiber, the first laser and the second laser are incident on the detection device.

[0026] Optionally, the light guiding component further includes a circulator. The circulator includes at least a first port, a second port, and a third port. The second laser emitted by the second light source component enters the first port. The second port is connected to the beam combiner, and the third port is connected to the imaging component.

[0027] Optionally, the light guiding component further includes a second optical fiber. The second optical fiber conducts the modulated second laser returned from the detection device to the imaging component.

[0028] Optionally, the endoscope processing device further includes a driving device configured to drive the detection device to rotate and / or move axially.

[0029] Optionally, the light guiding component includes a smooth ring rotatably connected to the detection device. The endoscope processing device further includes a first driving motor configured to drive the detection device to rotate.

[0030] An endoscope imaging system includes the detection device for photoacoustic imaging described above, or includes the endoscope processing device described above.

[0031] As can be seen from the above technical solutions, a detection device for photoacoustic imaging provided by the present invention includes a light guiding portion. The light guiding portion guides the first laser and the second laser to propagate from the proximal end to the distal end, and guides the first laser to be emitted from the distal end of the light guiding portion to the measured part, so that ultrasonic waves are generated in the measured part based on the action of the first laser. A photoacoustic modulation portion is provided at the distal end of the light guiding portion. The photoacoustic modulation portion is modulated by the ultrasonic waves to modulate the second laser, and the modulated second laser returns to the proximal end along the light guiding portion. An imaging result of the measured part can be obtained according to the modulated second laser.

[0032] The detection device for photoacoustic imaging of the present invention emits the first laser to the measured part to stimulate the measured part to generate ultrasonic waves, and uses the photoacoustic modulation portion to be modulated by the ultrasonic waves to modulate the second laser. Furthermore, an imaging result of the measured part is obtained based on the modulated second laser. Compared with the prior art, the present detection device can at least avoid using an ultrasonic transducer for emitting ultrasonic waves to the measured part and an ultrasonic transducer for receiving the ultrasonic waves reflected back by the measured part, can reduce the number of components used, reduce the cost and processing difficulty, and can reduce the diameter of the detection device, making it easier to detect parts with smaller cavity diameters (such as blood vessels).

[0033] The present invention also provides an endoscope processing device, which can achieve the above beneficial effects.

[0034] The present invention also provides an endoscope imaging system, which can achieve the above beneficial effects. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] In order to more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the following will briefly introduce the drawings required for use in the description of the embodiments or the prior art. Obviously, the drawings in the following description are only some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0036] Figure 1 Schematic diagram of a detection device for photoacoustic imaging provided by an embodiment of the present invention;

[0037] Figure 2 Schematic diagram of a detection device for photoacoustic imaging provided by another embodiment of the present invention;

[0038] Figure 3 Schematic diagram of the optical path for guiding the first laser emitted by the light guiding part according to an embodiment of the present invention;

[0039] Figure 4 Schematic diagram of the optical path for guiding the first laser emitted by the light guiding part according to another embodiment of the present invention;

[0040] Figure 5 Schematic diagram of a detection device for photoacoustic imaging provided by another embodiment of the present invention;

[0041] Figure 6 Schematic diagram of an endoscope processing device provided by an embodiment of the present invention;

[0042] Figure 7 Schematic diagram of an endoscope processing device provided by another embodiment of the present invention. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0043] In order to enable those skilled in the art to better understand the technical solutions in the present invention, the following will clearly and completely describe the technical solutions in the embodiments of the present invention with reference to the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, rather than all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present invention.

[0044] Please refer to Figure 1 , Figure 1Schematic diagram of a detection device for photoacoustic imaging provided in this embodiment. As shown in the figure, the detection device includes a light guiding part 100. The light guiding part 100 is used to guide the first laser and the second laser to propagate from the proximal end to the distal end, and guide the first laser to be emitted from the distal end of the light guiding part 100 to the part to be measured, so that ultrasonic waves are generated in the part to be measured based on the action of the first laser.

[0045] A photoacoustic modulation part 101 is arranged at the distal end of the light guiding part 100. The photoacoustic modulation part 101 is modulated by ultrasonic waves on the second laser, and the modulated second laser returns to the proximal end via the light guiding part 100.

[0046] The distal end of the light guiding part 100 refers to the end of the light guiding part 100 close to the part to be measured, and the proximal end of the light guiding part 100 refers to the other end of the light guiding part 100 relative to the distal end. The light guiding part 100 guides the propagation of the first laser, emits the first laser to the part to be measured, and the biological tissue of the part to be measured absorbs the photon energy of the first laser and generates ultrasonic waves due to thermal expansion.

[0047] The ultrasonic waves generated in the part to be measured propagate to the photoacoustic modulation part 101. The photoacoustic modulation part 101 generates strain under the action of ultrasonic waves, thereby modulating the second laser and making the modulated second laser return. An imaging result of the part to be measured can be obtained according to the modulated second laser.

[0048] The detection device for photoacoustic imaging in this embodiment can at least avoid using an ultrasonic transducer for emitting ultrasonic waves to the part to be measured and an ultrasonic transducer for receiving the ultrasonic waves reflected back from the part to be measured. Therefore, the number of components used can be reduced, the diameter of the detection device can be reduced, and the processing is simpler.

[0049] In this embodiment, the specific manner in which the photoacoustic modulation part 101 is modulated by ultrasonic waves on the second laser is not limited, as long as the photoacoustic modulation part 101 can be modulated by ultrasonic waves on the second laser. The modulation of the second laser by the photoacoustic modulation part 101 includes but is not limited to changing the propagation form of the second laser or changing the energy magnitude of the second laser. Optionally, the working mode of the photoacoustic modulation part 101 can be: for the light incident on the photoacoustic modulation part 101, the photoacoustic modulation part 101 reflects back the light with the same wavelength as its own working wavelength; the photoacoustic modulation part 101 generates deformation under the action of ultrasonic waves, so that the working wavelength changes. Correspondingly, in this detection device, if the wavelength of the second laser is the same as the working wavelength of the photoacoustic modulation part 101, the second laser incident on the photoacoustic modulation part 101 will be reflected back.

[0050] The principle of using this detection device to image the measured part is as follows: A first laser is emitted to the measured part, and the biological tissue of the measured part is excited by the first laser to emit ultrasonic waves; the photoacoustic modulation unit 101 deforms under the action of the ultrasonic waves, causing the working wavelength of the photoacoustic modulation unit 101 to change; if the wavelength of the second laser changes continuously, as the working wavelength of the photoacoustic modulation unit 101 changes, when the wavelength of the second laser is the same as the working wavelength of the photoacoustic modulation unit 101, the second laser will be reflected back. By measuring the light intensity of the returned second laser, information about the measured part can be obtained based on the wavelength and light intensity of the returned second laser, thereby realizing imaging of the measured part.

[0051] The wavelength range of the second laser can be set in combination with the wavelength of the first laser and the type, structure, or working mode of the photoacoustic modulation unit 101. Since the working wavelength of the photoacoustic modulation unit 101 changes continuously during the detection process, the wavelength of the second laser needs to change in coordination with the photoacoustic modulation unit 191. The wavelength of the first laser can be set according to the situation of the measured part and the environment of the measured part in actual applications. Preferably, the first laser uses pulsed laser, and the energy of the pulsed laser is more concentrated, which helps to effectively excite the biological tissue of the measured part to generate ultrasonic waves when the first laser is emitted to the measured part.

[0052] In some existing probes for photoacoustic imaging, a laser ultrasonic transducer is used to convert laser into ultrasonic waves and emit the ultrasonic waves to the measured part. After the ultrasonic waves encounter the measured part, they are reflected back, and imaging is performed based on the received ultrasonic echoes. In such a probe, the received ultrasonic waves are the ultrasonic waves reflected back from the measured part. Compared with using such a probe for detection and imaging, the detection device in this embodiment emits a laser to the measured part, excites the measured part itself to generate ultrasonic waves through the laser, and performs imaging by collecting the ultrasonic waves generated by the measured part, making the detection sensitivity and specificity for the measured part better. And because it is based on the absorption of light by the measured part for imaging, the obtained image has a higher contrast, significantly higher than the contrast of the image obtained by the existing probe by collecting the ultrasonic waves reflected back from the measured part. Therefore, the obtained image is more conducive to distinguishing the microscopic structure and composition of biological tissues.

[0053] In addition, in some existing probes for photoacoustic imaging, an ultrasonic transducer is used to receive the returned ultrasonic waves, which not only makes the probe large in volume and diameter, but also has a limited working frequency band for the ultrasonic transducer, and is also easily affected by electromagnetic interference from the internal and external environments, affecting the signal-to-noise ratio and sensitivity of imaging. However, the detection device in this embodiment uses a photoacoustic modulation unit to collect ultrasonic waves and performs imaging by modulating the laser, avoiding the use of an ultrasonic transducer, which can not only reduce the volume, but also reduce the electromagnetic interference from the internal and external environments, thereby improving the accuracy of the imaged object.

[0054] Preferably, the absolute value of the difference between the wavelength of the first laser and the operating wavelength of the photoacoustic modulation unit 101 is greater than or equal to a preset value, so that the interval between the wavelength of the first laser and the operating wavelength of the photoacoustic modulation unit 101 is relatively large, avoiding the photoacoustic modulation unit 101 modulating the first laser and affecting the imaging accuracy. In this embodiment, the specific value of the preset value is not limited, as long as it can satisfy that the photoacoustic modulation unit 101 does not modulate the first laser and affect the imaging result. In practical applications, the preset value can be set according to the type, structure, and working mode of the photoacoustic modulation unit 101.

[0055] Optionally, the photoacoustic modulation unit 101 can be disposed on the end face at the distal end of the light guiding unit 100. Refer to Figure 2 , Figure 2 FIG. is a schematic diagram of a detection device for photoacoustic imaging provided in another embodiment. The solid line with an arrow in the figure represents the first laser, and the dashed line with an arrow represents the second laser. As shown, the photoacoustic modulation unit 101 is disposed on one end face of the light guiding unit 100, so that when the second laser propagating along the light guiding unit 100 reaches the photoacoustic modulation unit 101, it can return along the light guiding unit 100 after being modulated by the photoacoustic modulation unit 101.

[0056] Preferably, the photoacoustic modulation unit 101 can be disposed inside the light guiding unit 100. Refer to Figure 1 shown, Figure 1 the solid line with an arrow in the figure represents the first laser, and the dashed line with an arrow represents the second laser. The photoacoustic modulation unit 101 is disposed inside the distal end of the light guiding unit 100. Such a setting can avoid the photoacoustic modulation unit 101 occupying extra space, which helps to reduce the diameter of the detection device.

[0057] Optionally, the photoacoustic modulation unit 101 can adopt a Bragg grating. The operating wavelength of the photoacoustic modulation unit 101 is determined by the period of the Bragg grating. When ultrasonic waves act on the Bragg grating, the grating will be compressed, causing the period of the grating to change, thereby changing its operating wavelength. Preferably, a π-phase shift Bragg grating can be used. The π-phase shift Bragg grating has a steeper slope, thus responding to ultrasonic waves in a larger frequency range, which helps to improve the imaging accuracy.

[0058] Optionally, the light guiding unit 100 can adopt an optical fiber. Conducting laser through the optical fiber can reduce the loss of light energy. Correspondingly, the photoacoustic modulation unit 101 can be a Bragg grating. This enables the light guiding part of this device to select a single optical fiber, greatly reducing the outer diameter of the main part of the detection device, and enabling the detection of parts with a smaller cavity diameter (such as blood vessels). Through the existing technology of processing optical fibers, the Bragg grating can be formed inside it, so that the function of the photoacoustic modulation unit 101 can be realized without additional components.

[0059] Optionally, the distal end face of the light guide portion 100 is an inclined plane, so that the first laser is emitted laterally from the light guide portion 100. That the end face of one end of the light guide portion 100 is an inclined plane means that the angle between the end face and the axis of the light guide portion 100 is greater than 0 degrees and less than 90 degrees. For reference, it can be combined with Figure 3 as shown Figure 3 Figure 3 is a schematic diagram of the optical path for guiding the first laser to be emitted by the light guide portion in an embodiment. As shown in the figure, the distal end face 102 of the light guide portion 100 is an inclined plane, and the light is refracted or totally reflected on the inclined plane 102 of the light guide portion 100, so as to be emitted laterally from the light guide portion 100. Since in the actual application scenario of the detection device, it is usually necessary to detect the parts located on the side wall, such as the side walls of blood vessels, bronchi, esophagus or intestines, the outgoing light of the light guide portion 100 in this detection device is emitted laterally, so that the detected part can be irradiated and the detected part can be detected and imaged.

[0060] Optionally, the detection device may include a reflection element for reflecting the first laser emitted from the light guide portion 100, so that the first laser is emitted towards the detected part. For reference, it can be combined with Figure 4 , Figure 4 Figure 4 is a schematic diagram of the optical path for guiding the first laser to be emitted by the light guide portion in another embodiment. As shown in the figure, the distal end face 102 of the light guide portion 100 is a flat plane, and the outgoing light of the light guide portion 100 is reflected by the reflection element 103, so that the light can irradiate the detected part located laterally, such as the side walls of blood vessels, bronchi, esophagus or intestines.

[0061] Furthermore, to obtain a two-dimensional image or a three-dimensional image of the detected part, the detection device needs to be able to move and irradiate the laser at different positions of the detected part for imaging. To meet this requirement, the detection device may further include a driving device, and the driving device can be connected to the proximal end of the light guide portion 100 for driving the light guide portion 100 to rotate and / or axially move (which can be a two-way advancing and retreating movement or a one-way retracting movement). Thus, the light guide portion 100 can irradiate the laser at different positions of the detected part.

[0062] In this embodiment, the specific structure of the driving device is not limited, as long as it can realize the rotation and / or axial movement of the light guiding part 100. As an alternative embodiment, the driving device may include a driving transmission part, which is wrapped around the light guiding part 100 and at least exposes the emission area of the first laser and the photoacoustic modulation part 101. The driving transmission part is relatively stationary with the light guiding part 100 and is used to drive the light guiding part 100 to rotate. The driving transmission part exposes the photoacoustic modulation part 101 so that the photoacoustic modulation part 101 can be fully and effectively affected by ultrasonic waves. The driving transmission part can transfer the rotational torque from the proximal end of the light guiding part 100 to the distal end, thereby driving the light guiding part 100 to rotate. In this embodiment, the specific structure of the driving transmission part is not limited, and various forms such as coils or shells can be used to wrap around the outside of the light guiding part 100. The material of the driving transmission part is generally metal.

[0063] Optionally, a smooth ring can be provided at the proximal end of the light guiding part 100. The driving transmission part is connected to the smooth ring, and the smooth ring is connected to the first driving motor. The first driving motor drives the smooth ring to rotate, and the smooth ring drives the driving transmission part to rotate, thereby realizing the driving of the light guiding part 100 to rotate. Reference can be made to Figure 5 , Figure 5 FIG. is a schematic diagram of a detection device for photoacoustic imaging provided for another embodiment. As shown in the figure, a coil 104 is wound around the outside of the light guiding part 100. The smooth ring 105 is connected to the coil 104, and the smooth ring 105 drives the coil 104 to rotate, thereby driving the light guiding part 100 to rotate, and a 360-degree rotation along the circumferential direction of the light guiding part 100 can be realized, so that two-dimensional imaging of the measured part can be realized. For existing probes using ultrasonic transducers, in order to realize the rotation of the probe, an optoelectronic slip ring needs to be used. In contrast, the detection device of this embodiment does not require an ultrasonic transducer, so an optoelectronic slip ring can be not used, and a single-channel smooth ring can be used, which not only simplifies the assembly but also reduces the cost.

[0064] Optionally, a second driving motor connected to the proximal end of the light guiding part 100 can also be provided. The second driving motor can drive the light guiding part 100 to move axially. Reference can be made to Figure 5 , and the second driving motor 106 is connected to the proximal end of the light guiding part 100. Thus, combined with the fact that the light guiding part 100 can rotate and move forward and backward, three-dimensional imaging of the measured part can be realized. The second driving motor can also be connected to the bracket of the first driving motor, and then the first driving motor and the light guiding part 100 as a whole are driven to move axially through a translational transmission mechanism.

[0065] Preferably, reference can be made to Figure 5As shown, the detection device may further include a housing 107, and the light guiding part 100 is disposed within the housing 107. The housing can protect the light guiding part 100, preventing some substances in the body from interfering with the light guiding part 100 when the detection device extends into the organism. Additionally, for the embodiment with a reflection element, the reflection element can be disposed within the housing. The driving and conducting part can also be disposed within the housing together with the light guiding part. The housing can be filled with a coupling agent to facilitate the transmission of ultrasonic waves.

[0066] A transparent window can be provided at the distal end of the housing 107. Alternatively, the entire housing 107 can be made of a transparent material, enabling the first laser emitted by the light guiding part 100 to pass through the housing 107 and irradiate the measured part. Optionally, the housing 107 can move synchronously with the light guiding part 100 in terms of advancing and retracting. Preferably, the housing 107 remains stationary when the light guiding part 100 moves in terms of advancing and retracting. The housing 107 can be made of a flexible and bendable material so that the detection device can enter a curved cavity for detection. The relative movement mode between the housing 107 and the light guiding part 100 can be set according to actual scenario requirements. The connection structure at the proximal end of the light guiding part 100 can be designed accordingly based on the required relative movement mode between the housing 107 and the light guiding part 100.

[0067] The driving device can also be connected to the proximal end of the above-mentioned driving and conducting part or the above-mentioned housing to achieve driving the overall movement of the detection device. The connection relationship depends on the setting mode of the above-mentioned structure and the requirements for the movement mode of the detection device in the application scenario.

[0068] In another feasible embodiment, by using a transmission mechanism in the prior art, the rotation of the output shaft of the driving motor can be converted into a helical motion. That is, by using a single driving motor in cooperation with a transmission mechanism, it is also possible to simultaneously achieve the rotation and axial movement of the light guiding part in the present invention.

[0069] Of course, the above-mentioned multiple preferred solutions do not constitute a limitation to the protection scope of the present invention. The detection device of the present invention can be a device that only includes a light guiding part and a photoacoustic modulation part. This device can rely on any other possible form of peripheral device to move to achieve the subsequent imaging process. The device that only includes a light guiding part and a photoacoustic modulation part can also solve the technical problem of the large probe diameter referred to in the background art, and the above-mentioned preferred solutions can provide further technical effects.

[0070] Correspondingly, please refer to Figure 6 , Figure 6Schematic diagram of an endoscope processing device provided in this embodiment. As shown in the figure, the endoscope processing device includes a first light source assembly 201, a second light source assembly 202, a light guiding assembly (not shown), and an imaging assembly 203. The first light source assembly 201 is used to emit a first laser, the second light source assembly 202 is used to emit a tunable second laser, and the light guiding assembly conducts the first laser and the second laser to the detection device 200.

[0071] The detection device 200 can adopt the detection device in the foregoing embodiment to emit the first laser to the measured part, so that ultrasonic waves are generated in the measured part based on the action of the first laser, and the second laser is modulated by the ultrasonic waves. The imaging assembly 203 is used to perform imaging based on the modulated second laser returned by the detection device 200. In this embodiment, it is not excluded to use other detection devices 200 with similar functions.

[0072] In the endoscope processing device of this embodiment, the detection device 200 emits the first laser to the measured part, stimulates the measured part to generate ultrasonic waves, and the second laser is modulated by the action of the ultrasonic waves, and the modulated second laser is returned. The imaging assembly 203 obtains the imaging result of the measured part based on the modulated second laser. Compared with the prior art, the detection device used in this endoscope processing device can at least avoid using an ultrasonic transducer for emitting ultrasonic waves to the measured part and an ultrasonic transducer for receiving ultrasonic waves reflected back from the measured part, can reduce the number of components used, and can reduce the diameter of the detection device. The endoscope processing device of this embodiment provides a simple solution for photoacoustic imaging to realize the emission of light source and the imaging of the returned optical signal.

[0073] During the detection process, the wavelength of the second laser emitted by the second light source assembly 202 is constantly changing. Correspondingly, during the detection of the measured part, the first laser is emitted to the measured part, and the biological tissue of the measured part is stimulated by the first laser to emit ultrasonic waves; the working wavelength of the detection device 200 changes under the action of the ultrasonic waves; at the same time, the wavelength of the second laser is constantly changing. As the working wavelength of the detection device 200 changes, if the wavelength of the second laser is consistent with the working wavelength of the detection device 200, the propagation form or the energy magnitude of the second laser will change, so as to realize the modulation of the second laser. The information of the measured part can be obtained according to the wavelength and light intensity of the returned second laser, so as to realize the imaging of the measured part.

[0074] In this embodiment, the change mode of the wavelength of the second laser during the detection process is not limited, and the change mode may be, but is not limited to, changing at a constant rate or the rate of change of the wavelength of the second laser is not fixed. Preferably, the wavelength of the second laser changes at a constant rate during the detection process, that is, the wavelength of the second laser changes uniformly, which helps to effectively collect ultrasonic waves of various frequencies generated by the measured part and improve the accuracy of imaging.

[0075] Preferably, the absolute value of the difference between the wavelength of the first laser emitted by the first light source assembly 201 and the working wavelength of the detection device 200 is greater than or equal to a preset value, so that the interval between the wavelength of the first laser and the working wavelength of the detection device 200 is relatively large, avoiding the detection device 200 modulating the first laser and affecting the imaging accuracy. In this embodiment, the specific value of the preset value is not limited, as long as it can satisfy that the detection device 200 does not modulate the first laser and affect the imaging result.

[0076] When the detection device in the foregoing embodiment is adopted, the photoacoustic modulation unit selects a Bragg grating, and the period of the Bragg grating determines the working wavelength of the detection device 200. At this time, the parameters of the Bragg grating, the second light source assembly, and the first light source assembly can be reasonably set to achieve the above imaging and avoid affecting imaging.

[0077] Optionally, the light guiding assembly may include a beam combiner and a first optical fiber. The beam combiner is used to combine the optical fiber for transmitting the first laser and the optical fiber for transmitting the second laser into the first optical fiber, and the first laser and the second laser are conducted to the detection device 200 through the first optical fiber. Transmitting light through the optical fiber and the beam combiner can reduce the loss of light energy and make the system structure compact.

[0078] Optionally, the detection device 200 can be directly connected to the imaging assembly 203. Preferably, the detection device 200 can be connected to the imaging assembly 203 through a second optical fiber.

[0079] Optionally, the light guiding assembly may further include a circulator. The circulator includes at least a first port, a second port, and a third port. The second laser emitted by the second light source assembly 202 enters the first port, the second port is connected to the beam combiner, and the third port is connected to the imaging assembly 203. Preferably, each light source assembly, the circulator, and the beam combiner are connected to each other through optical fibers, which can reduce the loss of light energy and reduce external interference.

[0080] For reference Figure 7 , Figure 7Schematic diagram of an endoscopic processing device provided for another embodiment. As shown in the figure, the first light source assembly 201 includes a first light source 206 and a first coupler 207. The first light source 206 and the beam combiner 204 are connected by an optical fiber through the first coupler 207. The second light source assembly 202 includes a second light source 208 and a second coupler 209. The second light source 208 and the first port ① of the circulator 205 are connected by an optical fiber through the second coupler 209.

[0081] The second port ② of the circulator 205 is connected to the beam combiner 204 by an optical fiber. The beam combiner 204 combines the optical fiber for transmitting the first laser connected from the first coupler 207 and the optical fiber for transmitting the second laser connected to the second port of the circulator 205 into one optical fiber, that is, the first optical fiber. The first optical fiber is connected to the detection device 200.

[0082] The imaging assembly 203 includes a photoelectric device 210, an acquisition card 211, and a display device 212. The third port ③ of the circulator 205 is connected to the photoelectric device 210 by an optical fiber. The photoelectric device 210 converts the returned second laser into an analog signal and transmits the analog signal to the acquisition card 211. The acquisition card 211 converts the analog signal into a digital signal, forms an image according to the digital signal, and the obtained image is displayed through the display device 212.

[0083] In a specific example, the modulation frequency of the first laser is 1 KHz to 20 KHz, the wavelength range is 500 nm to 2000 nm, and the pulse width of the first laser is 10 ps to 20 ns. The wavelength range of the second laser is 500 nm to 2000 nm, and the tuning rate is 0.1 nm / s to 30 nm / s. The absolute value of the difference between the wavelength of the first laser and the working wavelength of the photoacoustic modulation unit 101 is greater than or equal to 30 nm.

[0084] The first light source 206 is a pulsed laser with a modulation frequency of 1 KHz to 20 KHz. The second light source 208 is a tunable laser. The core diameter of the first optical fiber is 2 μm to 500 μm. The photoelectric device 210 can be a photodiode.

[0085] In another feasible embodiment, the light guiding assembly further includes a smooth ring connected to the detection device, and the endoscopic processing device further includes a first driving motor for driving the detection device to rotate. When combined with the foregoing embodiments, the smooth ring can be connected to the beam combiner through a first optical fiber. The first driving motor can drive the smooth ring to rotate. The addition of a second driving motor or replacement with a single driving motor as in the foregoing embodiments can also be referred to. For the specific transmission structure and connection relationship, reference can be made to the foregoing embodiments and the prior art. When a second driving motor is provided to drive the detection device to move axially, the first driving motor can be fixed on the bracket, and the second driving motor pulls the bracket to slide axially. The first optical fiber can be bent to cooperate with their axial movement, so that components such as the beam combiner connected to the proximal end of the first optical fiber can be in a stationary state.

[0086] It should be noted that the foregoing embodiments do not limit the components and structures included in the detection device and the endoscopic processing device respectively. For example, only a light guiding part and a photoacoustic modulation part (a driving conduction part, a housing, etc. can also be added) can be provided in the detection device, and a light guiding assembly (including a smooth ring, a first optical fiber, a beam combiner, a circulator, etc.), a first light source assembly, a second light source assembly, an imaging assembly, a driving device, etc. can be provided in the endoscopic processing device. Or, the smooth ring can be provided in the detection device (for example, at the proximal joint); furthermore, the driving device can also be provided in the detection device, and so on. Any detection device with any setting method or any endoscopic processing device with any setting method, as long as it can solve the technical problems described in the background art of the present invention, is within the protection scope of the present invention.

[0087] The present invention also provides an endoscopic imaging system, including the detection device for photoacoustic imaging in the foregoing embodiments, or including the endoscopic processing device in the foregoing embodiments.

[0088] Specifically, referring to any one of the detection devices in the foregoing embodiments, an endoscopic processing device that can cooperate with it to form a complete system in the foregoing embodiments can be combined with it to form the endoscopic imaging system of this embodiment, or other possible endoscopic processing devices not mentioned in the present invention can be combined. Conversely, any one of the foregoing endoscopic processing devices can be combined with the detection devices mentioned above or other unmentioned detection devices to form the endoscopic imaging system of this embodiment.

[0089] In one embodiment, only a light guiding part and a photoacoustic modulation part (a driving conduction part, a housing, etc. can also be added) can be provided in the detection device, and a light guiding assembly (including a smooth ring, a first optical fiber, a beam combiner, a circulator, etc.), a first light source assembly, a second light source assembly, an imaging assembly, a driving device, etc. can be provided in the endoscopic processing device. This makes the structural design and processing technology of the interface between the two simpler (only optical signals need to be transmitted), the disinfection of the detection device part is more convenient, and if the detection device part is used as a consumable, the loss cost can also be reduced.

[0090] The above has introduced in detail the detection device, endoscope processing device and imaging system for photoacoustic imaging provided by the present invention. Specific examples are used in this article to elaborate on the principle and implementation manner of the present invention. The description of the above embodiments is only used to help understand the method and its core idea of the present invention. It should be noted that for those of ordinary skill in the art, without departing from the principle of the present invention, several improvements and modifications can be made to the present invention, and these improvements and modifications also fall within the protection scope of the claims of the present invention.

Claims

1. A detection device for photoacoustic imaging, characterized in that, It includes a light guiding part which is used to guide the first laser and the second laser to propagate from the proximal end to the distal end, so that the first laser is emitted from the distal end of the light guiding part to the measured part, and ultrasonic waves are generated in the measured part based on the action of the first laser, and the wavelength of the second laser is constantly changing; A photoacoustic modulation part is arranged at the distal end of the light guiding part. The photoacoustic modulation part is used to reflect back the light with a wavelength consistent with its own working wavelength. The photoacoustic modulation part deforms under the action of the ultrasonic waves, so that the working wavelength of the photoacoustic modulation part changes. If the wavelength of the second laser is consistent with the working wavelength of the photoacoustic modulation part, the second laser is reflected back, and the second laser returns to the proximal end via the light guiding part.

2. The detection device for photoacoustic imaging according to claim 1, wherein The photoacoustic modulation part includes a Bragg grating.

3. The detection device for photoacoustic imaging according to claim 1, wherein The photoacoustic modulation part is arranged inside the light guiding part.

4. The detection device for photoacoustic imaging according to claim 1, characterized in that, The distal end face of the light guiding part is an inclined plane, so that the first laser is emitted to the side of the light guiding part.

5. The detection device for photoacoustic imaging according to claim 1, characterized in that It further includes a reflecting element, which is used to reflect the first laser emitted from the light guiding part, so that the first laser is emitted to the measured part.

6. The detection device for photoacoustic imaging according to claim 5, wherein The distal end face of the light guiding part is a flat plane.

7. The detection device for photoacoustic imaging according to claim 1, wherein The detection device further includes a driving and conducting part, which is coated on the light guiding part and at least exposes the emission area of the first laser and the photoacoustic modulation part. The driving and conducting part is relatively stationary with respect to the light guiding part and is used to transmit a rotational torque.

8. The detection device for photoacoustic imaging according to claim 1, characterized in that The detection device further includes a smooth ring connected to the light guiding part.

9. The detection device for photoacoustic imaging according to claim 1, characterized in that, It further includes a housing, and the light guiding part is arranged inside the housing.

10. The detection device for photoacoustic imaging according to any one of claims 1-9, characterized in that, It further includes a driving device, which is used to drive the light guiding part to rotate and / or move axially.

11. An endoscope processing device is connected to a detection device for photoacoustic imaging, characterized in that, It includes a first light source component, a second light source component, a light guiding component and an imaging component; The first light source component is used to emit the first laser, and the second light source component is used to emit a tunable second laser, and the wavelength of the second laser is constantly changing; The light guiding component is used to conduct the first laser and the second laser to the detection device, and conduct the modulated second laser returned by the detection device to the imaging component. The working wavelength of the detection device changes under the action of ultrasonic waves. As the working wavelength of the detection device changes, if the wavelength of the second laser is consistent with the working wavelength of the detection device, the detection device changes the propagation form or the energy magnitude of the second laser, so as to realize the modulation of the second laser; The imaging component is used to perform imaging based on the modulated second laser returned by the detection device.

12. The endoscopic treatment device according to claim 11, characterized in that, During the detection process, the wavelength of the second laser emitted by the second light source component is constantly changing.

13. The endoscopic processing device according to claim 11, wherein, The absolute value of the difference between the wavelength of the first laser and the working wavelength of the detection device is greater than or equal to a preset value.

14. The endoscopic processing device according to claim 11, wherein, The light guiding component includes a beam combiner and a first optical fiber. The beam combiner is used to combine the optical fiber transmitting the first laser and the optical fiber transmitting the second laser into the first optical fiber, and conduct the first laser and the second laser to the detection device through the first optical fiber.

15. The endoscopic treatment device according to claim 14, wherein The light guiding component further includes a circulator, the circulator includes at least a first port, a second port and a third port, the second laser emitted by the second light source component enters the first port, the second port is connected to the beam combiner, and the third port is connected to the imaging component.

16. The endoscopic treatment device according to claim 14, wherein The light guiding component further includes a second optical fiber, and the second optical fiber conducts the modulated second laser returned from the detection device to the imaging component.

17. The endoscopic processing device according to any one of claims 11-16, characterized in that, It further includes a driving device for driving the detection device to rotate and / or move axially.

18. The endoscopic treatment device according to claim 11, wherein, The light guiding component includes a smooth ring connected to the detection device, and the endoscopic processing device further includes a first driving motor for driving the detection device to rotate.

19. An endoscopic imaging system, characterized in that, It includes the detection device for photoacoustic imaging according to any one of claims 1-10, or includes the endoscopic processing device according to any one of claims 11-18.

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