Detection components and photoacoustic imaging equipment

Abstract

The present invention provides a detection assembly and a photoacoustic imaging device, comprising an imaging probe and a depth switching element. The imaging probe comprises an acoustic field source and a light guide for connecting to a trigger light source. The depth switching element is connected to the light guide, and the light guide has a light-emitting coverage area. The light-emitting coverage area is coupled with an active area of ​​the acoustic field source on the outside of the imaging probe to form a detection area. The depth switching element is used to adjust the distance from the light-emitting coverage area to the imaging probe. The detection assembly of the present invention can adjust the distance from the detection area to the acoustic field source, thereby expanding the detectable range of the detection assembly. Increasing the distance from the light-emitting coverage area to the imaging probe can increase the distance from the detection area to the imaging probe, thereby detecting deeper body tissues. Reducing the distance from the light-emitting coverage area to the imaging probe can reduce the distance from the detection area to the imaging probe, thereby detecting shallower body tissues without the need to use different imaging probes.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a detection component and a photoacoustic imaging device. Background Art

[0002] Photoacoustic endoscopic imaging technology can be used to obtain medical scans and provide a basis for disease diagnosis. Existing photoacoustic endoscopic imaging probes can only detect tissue within a specific depth range within the body. The imaging probe's detection range cannot cover shallower or deeper tissues in the body, making it difficult to obtain high-resolution, complete images of lesions. Summary of the Invention

[0003] In view of this, the present invention provides a detection component and a photoacoustic imaging device with a larger detection range to obtain clearer and more complete lesion image information.

[0004] The detection assembly of the present invention includes an imaging probe and a depth switching component. The imaging probe includes an acoustic field source and a light guide for connecting a trigger light source. The depth switching component is connected to the light guide. The light guide has a light-emitting coverage area. The light-emitting coverage area and the active area of ​​the acoustic field source are coupled outside the imaging probe to form a detection area. The depth switching component is used to adjust the distance from the light-emitting coverage area to the imaging probe.

[0005] Compared with the prior art, the detection assembly of the present invention can achieve the purpose of changing the distance between the detection area and the imaging probe along the radial direction of the imaging probe by adjusting the distance from the detection area to the sound field source, thereby expanding the detectable range of the detection assembly. Increasing the distance from the light coverage area to the imaging probe can increase the distance from the detection area to the imaging probe, thereby detecting deeper body tissues. Reducing the distance from the light coverage area to the imaging probe can reduce the distance from the detection area to the imaging probe, thereby detecting shallower body tissues without the need to use different imaging probes.

[0006] In some embodiments, the depth detection switching member includes a feeding member connected to the light guide member and a driving member for driving the feeding member, and the feeding member is reciprocatingly movable along the axial direction of the light guide member.

[0007] With such an arrangement, the light guide can be driven to move axially according to the depth of the tissue to be detected to change the position of the light output coverage area, thereby changing the position of the detection area.

[0008] In some embodiments, the end of the light guide close to the sound field source includes a light emitting portion, and an obtuse angle is formed between the axis of the light guide away from the sound field source and the light emitting direction of the light emitting portion.

[0009] In some embodiments, the feeding member includes a silk sleeve, the light guide member is an optical fiber fixedly installed in the silk sleeve, the two ends of the optical fiber extend from the two ends of the silk sleeve to connect to the trigger light source and form a light output part, and the driving member includes a motor that drives the silk sleeve to move axially back and forth.

[0010] In some embodiments, the invention further comprises a core having a through hole, the silk sleeve can be slidably extended into the core, the optical fiber passes through the through hole and extends out of the core, and the silk sleeve is gap-fitted with the inner wall of the core; and / or, there is a lubricant between the silk sleeve and the inner wall of the core.

[0011] In some embodiments, a capsule shell is further included, which includes a sleeve portion, a hollow portion and an assembly portion arranged in sequence, the sleeve portion is sleeved with a core, the light output portion is movably arranged in the hollow portion, the hollow portion is provided with a side through hole for the light output portion to reflect light, and the sound field source is installed in the assembly portion.

[0012] In some embodiments, the end of the light guide close to the sound field source includes a light emitting portion, and the light emitting portion forms an inclination angle θ with the axial direction of the light guide, where 18°≤θ≤40°; the maximum displacement of the driving member driving the feeding member to move back and forth is d, where 2㎜≤d≤3㎜.

[0013] In some embodiments, there are multiple light guides, and the light output coverage areas of the multiple light guides are staggered and distributed outside the imaging probe. The depth switching component selects different light guides to connect with the trigger light source to select the light output coverage areas at different positions to couple with the active area.

[0014] With such an arrangement, the light guide coupled with the acoustic field source can be switched according to the depth of the tissue to be detected, so that the active area is coupled with different light-emitting coverage areas and the position of the detection area is changed.

[0015] In some embodiments, the end of the light guide close to the sound field source includes a light emitting portion, an obtuse angle is formed between the axial direction of the light guide away from the sound field source and the light emitting direction of the light emitting portion, and

[0016] The plurality of light-emitting portions are staggered and distributed along the axial direction of the light guide; and / or the angles between the plurality of light-emitting portions and the axial direction of the light guide are arranged differently.

[0017] In some embodiments, the sound field source includes an active side parallel to the axial direction of the light guide, and the active area extends from the active side along the radial direction of the light guide toward the outside of the sound field source.

[0018] In some embodiments, the light guide is an optical fiber, and one end of the optical fiber close to the sound field source is a ground bevel, which forms a light-emitting portion of the optical fiber for reflecting light.

[0019] The photoacoustic imaging device of the present invention includes a trigger light source, a coupling actuator, a data processing device and a detection component. The light guide is connected to the trigger light source. The detection component also includes a force transmission mechanism connected to the coupling actuator and provided with an acoustic field source and the light guide. The data processing device is connected to the acoustic field source. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] Figure 1 It is a partial structural schematic diagram of the detection assembly of the present invention;

[0021] Figure 2 A partial structural cross-sectional view of a detection assembly of the present invention;

[0022] Figure 3 generating a schematic diagram of a detection area for a detection assembly according to an embodiment of the present invention;

[0023] Figure 4 generating a schematic diagram of a detection area for a detection assembly according to another embodiment of the present invention;

[0024] Figure 5 It is a partial structural schematic diagram of the light guide of the detection assembly of the present invention;

[0025] Figure 6 A cross-sectional view of the ferrule of the detection assembly of the present invention;

[0026] Figure 7 A first schematic diagram of a capsule housing of a detection assembly of the present invention;

[0027] Figure 8 A second schematic diagram of the capsule housing of the detection assembly of the present invention;

[0028] Figure 9 Schematic diagram of the photoacoustic imaging device of the present invention.

[0029] Explanation of the reference numerals: 100, detection assembly; 10, sound field source; 11, active side; 20, light guide; 21, light output portion; 30, feed member; 40, insert; 41, hole; 42, sleeve hole; 43, second wire binding groove; 50, capsule shell; 51, sleeve portion; 52, hollow portion; 521, side through hole; 53, assembly portion; 54, first wire binding groove; 60, data transmission line; 70, force transmission mechanism; 80, light-transmitting cover; 200, trigger light source; 300, coupling actuator; 400, drive member; 500, data processing device; 600, image display device. DETAILED DESCRIPTION

[0030] The following will be combined with the accompanying drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the embodiments described are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0031] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by those skilled in the art to which this invention pertains. The terms used herein in the specification of the present invention are for the purpose of describing specific embodiments only and are not intended to limit the present invention. The term "or / and" as used herein includes any and all combinations of one or more of the associated listed items.

[0032] The present invention provides a detection component 100 and a photoacoustic imaging device including the detection component 100. The photoacoustic imaging device generates medical images of human organs and tissues based on the principle of photoacoustic imaging, and presents the morphological contours of the organs and tissues in the body through the medical images, thereby providing a basis for disease diagnosis.

[0033] The detection assembly 100 of the present invention includes an imaging probe for inserting into the body, such as Figure 1~Figure 2 As shown, the imaging probe includes an acoustic field source 10, a light guide 20, a core insert 40, a capsule shell 50 and a force transmission mechanism 70. The capsule shell 50 includes a sleeve portion 51, a hollow portion 52 and an assembly portion 53. The core insert 40 includes a distal end and a proximal end. The sleeve portion 51 is fixedly sleeved on the distal end of the core insert 40. One end of the force transmission mechanism 70 is connected to the proximal end of the core insert 40, and the other end of the force transmission mechanism 70 is used to connect to the coupling actuator 300. The light guide 20 is inserted into the core insert 40. One end of the light guide 20 is used to connect to the trigger light source 200, and the other end extends from the distal end of the core insert 40 and is located in the hollow portion 52. The hollow portion 52 is provided with a side through hole 521. The side through hole 521 allows the light in the light guide 20 to be emitted and directed to the outside of the imaging probe. The acoustic field source 10 is installed on the assembly portion 53 and is connected to a data transmission line 60. The data transmission line 60 is connected to the data processing device 500.

[0034] In addition to the detection assembly 100 of the present invention, the photoacoustic imaging device of the present invention also includes a trigger light source 200, a coupling actuator 300, a data processing device 500 and an image display device 600. Figure 9As shown, the light guide 20 is connected to the trigger light source 200 and can receive the light signal generated by the trigger light source 200. The light signal is transmitted in the light guide 20. The end of the light guide 20 extending from the distal end of the ferrule 40 includes a light output portion 21. The light signal is reflected by the light output portion 21 and emitted to the outside of the imaging probe through the side through-hole 521 of the hollow portion 52. The spatial area located outside the imaging detection and capable of being covered by the light signal is the light output coverage area of ​​the light guide 20, and the light output coverage area is also located outside the sound field source 10; the sound field source 10 can convert energy in the form of electrical energy, magnetic energy, etc. into mechanical energy and generate a sound field. The sound field acts outward from the active side 11 of the sound field source 10. The spatial area located outside the active side 11 and capable of being covered by the sound field is the active area of ​​the sound field source 10. The active area extends from the active side 11 along the radial direction of the imaging probe toward the sound field source 10 and the outside of the imaging probe.

[0035] It can be understood that in other embodiments, the photoacoustic imaging device does not include the image display device 600, and the data processing device 500 can be connected to an external display device to display images.

[0036] The light-emitting coverage area and the active area are both located outside the imaging probe and are coupled to each other. The overlapping area between the two in space forms the imaging probe's detection area, which is located on the side periphery of the imaging probe. The photoacoustic imaging device can generate medical images of organs or tissues in the body within the detection area. The data processing device 500 obtains detection data about the detection area through the data transmission line 60 and generates a detection image. The image display device 600 is used to present the detection image. The coupling actuator 300 is used to provide both the coupling of optical and electrical signals required for detection and the power required for the imaging probe to perform scanning movement within the body. The coupling actuator 300 outputs power to the force transmission mechanism 70, which drives the ferrule 40 and the capsule 50 to move within the body. The light-emitting portion 21 and the acoustic field source 10 move accordingly and change the positions of the light-emitting coverage area, the active area, and the detection area. This allows detection of organs and tissues at different locations within the body, or enables scanning detection of organs and tissues within the body.

[0037] See Figure 2 , see also Figures 6 to 8 The imaging probe has an overall columnar structure. The ferrule 40 and the capsule shell 50 are preferably coaxially connected. The sleeve portion 51, the hollow portion 52 and the assembly portion 53 are preferably an integrally formed structure. The common axis of the ferrule 40 and the capsule shell 50 is the axis of the imaging probe. The light guide 20 is arranged along the axial direction of the imaging probe. The end of the light guide 20 extending out of the distal end of the ferrule 40 and the sound field source 10 are arranged in sequence along the axial direction of the imaging probe. The distal end of the light guide 20 extending out of the ferrule 40, that is, the end of the light guide 20 relatively close to the sound field source 10 and forming the light output portion 21.

[0038] Furthermore, the ferrule 40 is provided with a through hole 41 and a sleeve hole 42 extending axially and interconnected. The through hole 41 and the sleeve hole 42 respectively penetrate the distal and proximal ends of the ferrule 40. The light guide 20 is disposed within the through hole 41 and the sleeve hole 42. The light guide 20 extends from the proximal end of the ferrule 40 through the sleeve hole 42 and then extends into the interior of the force transmission mechanism 70. The light guide 20 extends from the distal end of the ferrule 40 through the through hole 41 and then extends into the hollow portion 52. The capsule 50 and the ferrule 40 are also provided with a first wire binding groove 54 and a second wire binding groove 43, respectively. The first wire binding groove 54 and the second wire binding groove 43 can extend along the axial direction of the imaging probe. The data transmission line 60 is arranged within the first wire binding groove 54 and the second wire binding groove 43. This allows the data transmission line 60 to move with the imaging probe within the body, preventing the data transmission line 60 from being scattered. The data transmission line 60 extends from the ferrule 40 through the second wire binding groove 43 and then extends into the interior of the force transmission mechanism 70. In order to isolate the light emitting portion 21 from the body fluid, the imaging probe further includes a light-transmitting cover 80 installed at the distal end of the ferrule 40 , and the light-transmitting cover 80 accommodates the light emitting portion 21 .

[0039] In some embodiments, the acoustic field source 10 is a transducer, the active side 11 of the transducer is a plane parallel to the axis of the imaging probe, the light guide 20 is a single-mode optical fiber, the light output portion 21 is a plane inclined relative to the axial direction of the imaging probe, and the force transmission mechanism 70 is a torque spring disposed proximally of the ferrule 40. In other embodiments, the light guide 20 may also be a multimode optical fiber. Preferably, the end of the optical fiber serving as the light guide 20, which is relatively close to the acoustic field source 10, is polished and beveled. The polished bevel is obtained by polishing the end of the optical fiber. The polished bevel forms the light output portion 21 for reflecting the light signal. Using the polished bevel as the light output portion 21 eliminates the reflective prism used as the light output portion 21 in existing similar products. This reduces the radial dimensions of the imaging probe, achieving an overall lighter and narrower imaging probe, reducing the number of light propagation interfaces and thereby reducing energy loss in light propagation, thereby improving light transmission efficiency. This allows the imaging probe to more easily enter narrow internal environments and improve its ability to pass through curved cavities.

[0040] Further, see Figure 2 、 Figure 7-Figure 8 The assembly portion 53 is provided with an insertion hole, the shape of the transducer matches the insertion hole, the transducer is fixedly embedded in the insertion hole, and the transducer as a whole has a flat structure. Compared with existing similar products using annular transducers, the flat transducer is easy and quick to install, and there is no need to process a center hole or arc surface for the transducer, thereby avoiding the problem of difficult processing of annular transducers. The active side 11, as part of the outer peripheral side of the entire imaging probe, can improve the receiving sensitivity of the transducer, which is conducive to obtaining high-resolution images in a small space.

[0041] It can be understood that in other embodiments, a reflector can also be set at the end of the light guide 20 relatively close to the sound field source 10, and the inner diameter of the capsule shell 50 can be increased to accommodate the reflector. The reflector is used to reflect the light signal in the light guide 20 and serve as the light output portion 21 of the light guide 20. An inclined surface inclined relative to the axial direction of the light guide 20 can also be processed at the end of the light guide 20 relatively close to the sound field source 10, and then a reflective coating is coated on the inclined surface. The reflective coating serves as the light output portion 21 of the light guide 20.

[0042] Existing imaging probes can only detect organs and tissues within a specific area in the body. The detection area is far outside the narrow cavity and cannot cover the narrow cavity, resulting in the inability to perform medical detection and imaging of tiny blood vessels, bronchi, and the urinary system. In some cases, high-resolution imaging detection of organs or tissues at different depths is also required. In view of this, the detection component 100 of the present invention also includes a detection depth switching component connected to the light guide 20. The detection depth switching component is used to adjust the distance from the light coverage area to the imaging probe, thereby adjusting the distance from the detection area to the imaging probe. Therefore, the detection area of ​​the detection component 100 is no longer limited to the specific spatial range of the imaging detection side, but can be flexibly changed as needed within a larger spatial range of the imaging detection side, thereby expanding the detectable range of the detection component 100.

[0043] Specifically, by increasing the distance from the light-emitting coverage area to the imaging probe, that is, by moving the light-emitting coverage area away from the sound field source 10 in the radial direction of the imaging probe, the distance from the detection area to the imaging probe can be increased, so that the detection area moves farther in the radial direction of the imaging probe, thereby detecting organs and tissues in the body at deeper locations; by reducing the distance from the light-emitting coverage area to the imaging probe, that is, by moving the light-emitting coverage area closer to the sound field source 10 in the radial direction of the imaging probe, the distance from the detection area to the imaging probe can be reduced, so that the detection area moves closer in the radial direction of the imaging probe, thereby detecting organs and tissues in the body at shallower locations. Therefore, the detection component 100 can reduce the distance from the light-emitting coverage area to the imaging probe so that the detection area covers a narrow cavity, thereby realizing medical detection and imaging of tiny blood vessels, bronchi, urinary system, etc., and can also detect organs or tissues at different depths.

[0044] See Figure 2~Figure 3 , see also Figure 7 and Figure 9 In some embodiments, the depth switching member includes a driving member 400 and a feeding member 30. The driving member 400 drives the feeding member 30. The feeding member 30 is reciprocally movable along the axial direction of the light guide 20 and is connected to the light guide 20. The axial direction of the light guide 20 is the same as the axial direction of the imaging probe. Figure 2 and Figure 3As shown, the horizontal direction represents the axial direction of the light guide 20 / the longitudinal direction of the optical fiber. The solid inclined arrow represents the light beam reflected by the light exit portion 21 when the light guide 20 is in the intermediate position, referred to as the intermediate position beam. Label II denotes the intersection of the intermediate position beam and the perpendicular to the active side 11 of the acoustic source 10. The perpendicular to the active side 11 of the acoustic source 10 extends in the radial direction of the imaging probe. Label II represents the detection area when the light guide 20 is in the intermediate position. When the light guide 20 is an optical fiber, the axial direction of the light guide 20 is the longitudinal direction of the optical fiber.

[0045] Further, see Figure 2 and Figure 5 The inclination angle of the light emitting portion 21 at the end of the light guide 20 relatively close to the sound field source 10 relative to the axial direction of the light guide 20 is: an obtuse angle is formed between the axial direction of the light guide 20 away from the sound field source 10 and the light emitting direction of the light emitting portion 21. The axial direction of the light guide 20 away from the sound field source 10 is Figure 2 and Figure 3 The horizontal left direction in the middle is the vector direction of the light guide 20 axially away from the sound field source 10 to the left. The light emitting direction of the light emitting portion 21 is the direction of the light reflected by the light emitting portion 21. Figure 3 The solid, tilted arrow representing the intermediate light beam is parallel to the light-emitting direction of the light-emitting portion 21. Because the driver 400 drives the light guide 20 to translate axially, the light guide 20 does not move in other directions, and the tilt of the light-emitting portion 21 does not change. The axis of the light guide 20, away from the sound source 10, maintains a fixed obtuse angle with the light-emitting direction of the light-emitting portion 21. The light-emitting footprint translates along the axial direction of the imaging probe as the light guide 20 translates. With this arrangement, most, or even all, of the light-emitting footprint is always located in front of the light guide 20, i.e., at the end of the light guide 20 closest to the sound source 10.

[0046] When it is necessary to reduce the distance from the detection area to the imaging probe, the driving member 400 outputs a thrust to the feed member 30, and the feed member 30 drives the light guide member 20 to move axially to the right. The length of the light guide member 20 extending out of the far end of the ferrule 40 increases, and the distance between the light output portion 21 and the sound field source 10 decreases. The light beam reflected by the light output portion 21 moves to the right. The dotted inclined arrow on the right side of the light beam in the middle position represents the light beam reflected by the light output portion 21 after the light guide member 20 moves to the right, which is simply referred to as the right-shifted light beam. Mark I is the intersection of the right-shifted light beam and the vertical line of the active side 11 of the sound field source 10. Mark I represents the detection area after the light guide member 20 moves to the right.

[0047] When it is necessary to increase the distance from the detection area to the imaging probe, the driving member 400 outputs a pulling force to the feed member 30, and the feed member 30 drives the light guide member 20 to move axially to the left. The length of the light guide member 20 extending out of the far end of the ferrule 40 is reduced, and the distance between the light output portion 21 and the sound field source 10 is increased. The light beam reflected by the light output portion 21 moves to the left. The dotted inclined arrow located on the left side of the light beam in the middle position represents the light beam reflected by the light output portion 21 after the light guide member 20 moves to the left, which is simply referred to as the left-shifted light beam. Mark III is the intersection of the left-shifted light beam and the vertical line of the active side 11 of the sound field source 10. Mark III represents the detection area after the light guide member 20 moves to the left.

[0048] As mentioned above, the tilt direction of the light emitting portion 21 does not change with the axial translation of the light guide 20. Figure 5 , an inclination angle θ is formed between the light emitting portion 21 and the axial direction of the light guide 20 close to the sound field source 10, 18°≤θ≤40°, when the transparent cover 80 is used to accommodate the light emitting portion 21, 20°≤θ≤40°, and the axial direction of the light guide 20 close to the sound field source 10 is Figure 2 and Figure 3 The horizontal right direction, that is, the vector direction of the axial center of the light guide 20 close to the sound field source 10, is set in this way to ensure that the detection area is always arranged along the radial direction of the imaging probe with the active side 11; the maximum displacement of the driving member 400 driving the feed member 30 to reciprocate along the axial direction of the imaging probe is d, 2㎜≤d≤3㎜, and in this way, the length of the light guide 20 extending out of the far end of the ferrule 40 changes by no less than 2㎜ and no more than 3㎜, the maximum activity of the light output part 21 along the axial direction of the imaging probe is between 2㎜ and 3㎜, the axial size of the hollow part 52 will not increase too much, and the axial length of the imaging probe can be limited to make it easier to enter a narrow cavity.

[0049] Optionally, the feed member 30 includes a hollow silk sleeve, the light guide 20 is an optical fiber that is inserted into the silk sleeve and fixedly connected to the inner wall of the silk sleeve, the axial direction of the silk sleeve is the same as the axial direction of the light guide 20, and the two ends of the optical fiber extend from the two ends of the silk sleeve, thereby respectively connecting the trigger light source 200 and forming a light output portion 21 for reflecting light, and the driving member 400 includes a motor that connects the silk sleeve and drives the silk sleeve to reciprocate along the axial direction. The silk sleeve can be a thin-walled metal sleeve that has sufficient strength to withstand the reciprocating driving force of the driving member 400. The motor can accurately control the amount of axial translation of the silk sleeve, thereby ensuring the precise axial displacement of the optical fiber, and the displacement accuracy of the light-emitting coverage area is improved accordingly, and ultimately the distance between the detection area and the sound field source 10 can be accurately controlled to achieve precise adjustment of the position of the detection area; in addition, the motor can also accurately control the amount of movement of the light-emitting part 21 along the axial direction of the imaging probe, to avoid excessive movement of the silk sleeve and the optical fiber, and to prevent the light-emitting part 21 from shrinking into the hole 41 or colliding with the sound field source 10; in addition, the motor can also control the light-emitting part 21 to move continuously within the maximum activity energy range to achieve scanning detection.

[0050] See Figure 2 and Figure 6 , Optionally, the inner diameter of the channeling hole 41 is smaller than the inner diameter of the sleeve hole 42, the inner diameter of the channeling hole 41 is close to the outer diameter of the optical fiber, and the inner diameter of the sleeve hole 42 is close to the outer diameter of the silk sleeve. The optical fiber extends from the end of the silk sleeve relatively close to the sound field source 10 and then passes through the channeling hole 41, and finally extends from the distal end of the ferrule 40. A clearance fit is formed between the optical fiber and the inner wall of the channeling hole 41 to ensure that the optical fiber moves smoothly in the channeling hole 41. The channeling hole 41 extends along the axial direction of the imaging probe, thereby guiding the light-emitting portion 21 to move back and forth along the axial direction of the imaging probe, and can also straighten the end of the optical fiber and limit the radial shaking of the light-emitting portion 21 along the imaging probe. The silk sleeve and the optical fiber sleeved by the silk sleeve are located in the sleeve hole 42, and the outer peripheral side of the silk sleeve forms a clearance fit with the inner wall of the sleeve hole 42. In order to reduce the sliding resistance between the silk sleeve and the ferrule 40, a lubricant is provided between the outer peripheral side of the silk sleeve and the inner wall of the sleeve hole 42, and the lubricant can be molybdenum disulfide.

[0051] In a second embodiment of the present invention, there are multiple light guides 20, each of which is a single optical fiber. Multiple optical fibers are clustered and run through the force transmission mechanism 70 and the ferrule 40. Each light outlet 21 of the multiple optical fibers extends from the distal end of the ferrule 40 and is located in the hollow portion 52. Each light outlet 21 can reflect the light beam in the optical fiber and make the light beam be emitted to the outside of the imaging probe through the side through-hole 521 provided in the hollow portion 52. Each light outlet 21 and the axial direction of the light guide 20 away from the sound field source 10 form an obtuse angle of equal or unequal size. Each light outlet 21 can reflect the light beam in the optical fiber toward the front of the light outlet 21 and form multiple light outlet coverage areas. Each light outlet coverage area is located at the corresponding guide In front of the light element 20, that is, in the axial direction of the light guide 20, the light output coverage area is located outside the length range of the light guide 20. The sound field can be entirely located within the length range of the light guide 20, or partially located within the length range of the light guide 20. The light output coverage areas of multiple light guides 20 are staggered on the outside of the imaging probe. The depth switching component can select different light guides 20 to connect to the trigger light source 200. The light guide 20 connected to the trigger light source 200 can receive the light signal and reflect the light beam to the outside of the imaging probe through the light output part 21, thereby selecting the light output coverage areas at different positions to overlap and couple with the action area of ​​the sound field source 10. Changing the light guide 20 connected to the trigger light source 200 can change the distance from the detection area to the imaging probe.

[0052] It should be noted that, in other embodiments, the light emitting coverage area does not have to be located in front of the light guide 20. In other words, in the axial direction of the light guide 20, the light emitting coverage area can be entirely located within the length range of the light guide 20, or partially located within the length range of the light guide 20, and the light emitting direction of the light emitting portion 21 can also be the radial direction of the imaging probe; in order to achieve adjustable radial distance between the detection area and the imaging probe, the sound field generated by the sound field source 10 can be within the length range of the light guide 20, and the active side 11 of the sound field source 10 can therefore be set to be inclined relative to the axial direction of the imaging probe, and the distance from the active side 11 to the axis of the imaging probe increases in the direction away from the light guide 20. With this arrangement, the sound field is located behind the sound field source 10, and at least a part of the sound field is located within the length range of the light guide 20.

[0053] The second embodiment of the present invention can omit the driving member 400 and the feeding member 30, and there is no need to drive the optical fiber to axially reciprocate in the force transmission mechanism 70 and the ferrule 40. Multiple optical fibers can serve as spare parts for each other, and damage or failure of one optical fiber will not affect the basic detection function of the detection component 100.

[0054] See Figure 4 Optionally, the length directions of the plurality of optical fibers are the same, and the length direction of each optical fiber away from the sound field source 10 forms an obtuse angle of equal or unequal size with the light output direction of the light output portion 21 of the optical fiber. Figure 4 The three solid arrows represent the light beams reflected by the three light emitting portions 21, and the light emitting direction of the light emitting portion 21 is the direction indicated by the solid arrow. The light emitting portions 21 of the multiple optical fibers are arranged one by one along the length direction of the optical fiber and are staggered. The length direction of the optical fiber is the axial direction of the imaging probe, and the length direction of the optical fiber away from the sound field source 10 is Figure 4 The horizontal left direction is the vector direction in the length direction of the optical fiber that is away from the sound field source 10 to the left. Figure 4 Marks I, II, and III in the middle represent detection areas at three different positions, respectively. The three detection areas are at different distances from the active side 11 in the radial direction of the imaging probe. The intersection of each reflected light beam and the vertical line of the active side 11 represents an overlapping part of a light-emitting coverage area and the active area.

[0055] It can be understood that in other embodiments, the angles between the multiple light-emitting portions 21 and the length direction of the optical fiber are set differently. In this way, the light-emitting directions of each light-emitting portion 21 are different, and multiple light-emitting coverage areas can be staggered on the outside of the sound field source 10.

[0056] The various technical features of the above-described embodiments can be combined arbitrarily. To make the description concise, not all possible combinations of the various technical features in the above-described 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.

[0057] Those skilled in the art should recognize that the above embodiments are merely intended to illustrate the present invention and are not intended to limit the present invention. Any appropriate changes and modifications to the above embodiments fall within the scope of the present invention as long as they are within the spirit of the present invention.

Claims

1. A photoacoustic imaging detection component, characterized in that: The imaging probe comprises an imaging probe and a depth-detection switching element, wherein the imaging probe comprises an acoustic field source (10) and a plurality of light guides (20) for connecting to a trigger light source (200), the depth-detection switching element is connected to the light guides (20), the light guides (20) having a light-emitting coverage area, the light-emitting coverage area and the active area of ​​the acoustic field source (10) being coupled outside the imaging probe to form a detection area, and the depth-detection switching element is used to adjust the distance from the light-emitting coverage area to the imaging probe; The light-emitting coverage areas of the plurality of light guide members (20) are staggeredly distributed outside the imaging probe, and the depth-detection switching member selects different light guide members (20) to be connected to the trigger light source (200), so as to select the light-emitting coverage areas at different positions to be coupled with the active area; The light guide (20) is a single-mode optical fiber or a multi-mode optical fiber. One end of the light guide (20) close to the sound field source (10) is a ground bevel, and the ground bevel forms a light exit portion (21) to reflect light signals.

2. The photoacoustic imaging detection assembly according to claim 1, wherein: The light exit portion (21) and the axial direction of the light guide (20) close to the sound field source (10) form an inclination angle θ, wherein 18°≤θ≤40°.

3. The photoacoustic imaging detection assembly according to claim 1, wherein: An obtuse angle is formed between the axial direction of the light guide (20) away from the sound field source (10) and the light emitting direction of the light emitting portion (21), and The plurality of light-emitting portions (21) are staggeredly distributed along the axial direction of the light-guiding element (20); and / or the angles between the plurality of light-emitting portions (21) and the axial direction of the light-guiding element (20) are differentially arranged.

4. The photoacoustic imaging detection assembly according to any one of claims 1 to 3, wherein: The sound field source (10) comprises an active side (11) parallel to the axial direction of the light guide (20), and the active region extends from the active side (11) along the radial direction of the light guide (20) toward the outside of the sound field source (10).

5. A photoacoustic imaging device, characterized in that The photoacoustic imaging detection component comprises a trigger light source (200), a coupling actuator (300), a data processing device (500), and the photoacoustic imaging detection component according to any one of claims 1 to 4, wherein the light guide (20) is connected to the trigger light source (200), the photoacoustic imaging detection component further comprises a force transmission mechanism (70) connected to the coupling actuator (300) and provided with the sound field source (10) and the light guide (20), and the data processing device (500) is connected to the sound field source (10).

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