Multifunctional femtosecond device for ophthalmology

Abstract

This invention relates to the field of femtosecond laser technology and discloses a multifunctional ophthalmic femtosecond device. The device includes: a scanning imaging module for emitting a probe beam and performing OCT imaging; a femtosecond laser scanning module for receiving the probe beam and irradiating the target tissue with the probe beam; the femtosecond laser scanning module for generating a femtosecond laser and focusing the femtosecond laser onto the target tissue; a surgical microscope module for receiving the probe beam and irradiating the target tissue; and the surgical microscope module for performing microscopic imaging. This invention integrates optical coherence tomography (OCT) technology, adding more imaging information to the original visible light image, which can effectively improve realignment accuracy and avoid the problem of separation and misalignment of corneal lenticule layers.

Description

Technical Field

[0001] This invention relates to the field of femtosecond laser technology, and specifically to a multifunctional ophthalmic femtosecond device. Background Technology

[0002] Femtosecond lasers are extremely short-pulse lasers commonly used in ophthalmic refractive surgeries and femtosecond cataract surgeries. During the procedure, a negative pressure suction device is often used to fix the eyeball, ensuring precise cutting of the cornea or lens. During femtosecond laser scanning, factors such as involuntary eye movements by the patient can cause the loss of this negative pressure suction, leading to surgical interruption or delay.

[0003] For refractive ophthalmic surgery, common approaches include elective re-operation or re-treatment. Elective re-treatment significantly impacts the patient's experience, while re-treatment typically involves re-aligning the initial incision area using a visible light camera with a watermark. However, the watermark formed by air bubbles from the initial incision area has very blurred boundaries and easily disappears, resulting in very low re-alignment accuracy, with an error of approximately 1mm. Clinically, lateral alignment accuracy should be less than 200µm to avoid ablation off-centering. Therefore, simply using a camera-guided watermark for re-alignment easily leads to secondary ablation off-centering, thus affecting the patient's postoperative visual quality. Furthermore, during femtosecond LASIK surgery, the corneal stroma is usually ablated twice: once in a slightly shallower area and once in a slightly deeper area. After ablation, a thin layer of corneal tissue is left between the two layers, which needs to be removed—the lenticule removal procedure. The current common practice is to perform the procedure under the eyepiece of a surgical microscope. The common practice is for doctors to judge the depth of the corneal lenticule by touch and the planar top view of the optical microscope objective. However, this method is prone to accidentally hooking the wrong corneal lenticule layer, which can lead to difficulties in lenticule removal or even failure.

[0004] Therefore, there is an urgent need for a multifunctional ophthalmic femtosecond laser device that can ensure accurate realignment during intensive treatment and provide more imaging information under optical microscope objectives. Summary of the Invention

[0005] In view of this, the present invention provides a multifunctional ophthalmic femtosecond device to solve the problems of low realignment accuracy and relatively simple imaging information in existing femtosecond devices.

[0006] In a first aspect, the present invention provides a multifunctional ophthalmic femtosecond laser device, the device comprising:

[0007] The scanning imaging module is used to emit a probe beam and perform OCT imaging;

[0008] The femtosecond laser scanning module is used to receive the probe beam and to irradiate the target tissue with the probe beam; the femtosecond laser scanning module is also used to generate femtosecond laser and focus the femtosecond laser onto the target tissue;

[0009] The surgical microscope module is used to receive the probe beam and direct it onto the target tissue; the surgical microscope module is also used for microscopic imaging.

[0010] In one optional implementation, the scanning imaging module includes: a fiber optic imaging unit, an optical path switching unit, and a planar scanning galvanometer;

[0011] The fiber optic imaging unit is used to emit a probe beam and transmit it to the optical path switching unit; the fiber optic imaging unit is used to perform first OCT imaging when the femtosecond laser scanning module receives the probe beam, and to perform second OCT imaging when the surgical microscope module receives the probe beam.

[0012] The optical path switching unit is used to switch between the first OCT imaging and the second OCT imaging.

[0013] The planar scanning galvanometer is positioned in the light output direction of the optical path switching unit.

[0014] In one optional implementation, the femtosecond laser scanning module includes a femtosecond laser, an optical Z-axis scanner, an electrically controlled optical path switching mirror, and an optical plane scanner arranged sequentially.

[0015] The femtosecond laser is used to generate femtosecond lasers, and the electrically controlled optical path switching mirror is used to receive the probe beam emitted by the optical path switching unit and / or the femtosecond laser emitted after being transmitted through the optical Z-axis scanner.

[0016] The electrically controlled optical path switching mirror is turned on when the optical path switching unit switches to the first OCT imaging, so as to transmit the received probe beam to the optical plane scanner; the electrically controlled optical path switching mirror is turned off when the optical path switching unit switches to the second OCT imaging.

[0017] An optical planar scanner is used to direct a probe beam onto the target tissue and / or to focus a femtosecond laser onto the target tissue;

[0018] The femtosecond laser scanning module also includes:

[0019] The first dichroic mirror is positioned in the light-emitting direction of the optical plane scanner and is used to reflect the probe beam or femtosecond laser.

[0020] The first objective lens, positioned in the first light-emitting direction of the first dichroic mirror, is used to focus the probe beam and / or femtosecond laser onto the target tissue;

[0021] A negative pressure ring is placed between the first objective lens and the target tissue to fix the target tissue.

[0022] The first visible light camera is set in the second light-emitting direction of the first dichroic mirror and is used to perform real-time imaging of the target tissue.

[0023] A laser diode is used to generate an indicator light spot, which is used to indicate the target cutting point on the target tissue.

[0024] In one optional implementation, the surgical microscope module is used to receive the reflected probe beam after being reflected by the planar scanning galvanometer when switching from the first OCT imaging to the second OCT imaging, and to irradiate the target tissue with the reflected probe beam;

[0025] The surgical microscope module includes, in sequence, an eyepiece, a beam splitter, an optical zoom lens, a second dichroic mirror, and a second objective lens; wherein, the second dichroic mirror is used to receive the reflected probe beam and irradiate the target tissue with the reflected probe beam;

[0026] The surgical microscope module also includes a second visible light camera, positioned in the light output direction of the beam splitter, for real-time imaging of the target tissue.

[0027] In one optional implementation, the fiber optic imaging unit includes:

[0028] A frequency-sweeping light source is used to generate a probe beam, which is emitted via optical fiber.

[0029] A coupler, positioned in the light output direction of the swept frequency light source, is used to split the probe beam into a sample arm beam and a reference arm beam.

[0030] The scanning acquisition imaging unit is used to perform OCT imaging based on the coherent reflection of the sample arm beam and the reference arm beam;

[0031] The optical path switching unit includes:

[0032] The first fiber optic path switcher is used to switch the sample arm beam to realize the imaging switch between the first OCT imaging and the second OCT imaging. When the first fiber optic path switcher is in the first OCT imaging mode, the sample arm beam is emitted to the electrically controlled optical path switching mirror through the first collimator. When the first fiber optic path switcher is in the second OCT imaging mode, the sample arm beam is emitted to the plane scanning galvanometer through the second collimator.

[0033] The second fiber optic path switcher is used to switch the reference arm beam to achieve imaging switching between the first OCT imaging and the second OCT imaging. When the first fiber optic path switcher is in the first OCT imaging state, the reference arm beam is emitted to the first high-reflection mirror through the third collimator. When the first fiber optic path switcher is in the second OCT imaging state, the reference arm beam is emitted to the second high-reflection mirror through the fourth collimator.

[0034] In one alternative implementation, the coupler includes:

[0035] A beam splitter, positioned in the light output direction of a swept frequency light source, is used to generate the sample arm beam and the reference arm beam.

[0036] An attenuator, located in the reference output direction of the beam splitter, is used to receive the reference arm beam and adjust the optical power intensity.

[0037] The first circulator is set in the sample output direction of the beam splitter to receive the sample arm beam. The sample arm beam that passes through the first circulator is emitted to the first fiber optic path switcher. The optical signal that is transmitted through the first fiber optic path switcher and returns along the original path will re-enter the first circulator and be transmitted to the beam combiner.

[0038] The second circulator is set in the output direction of the attenuator. The light beam emitted through the reference arm of the second circulator is sent to the second fiber optic path switcher. The light signal transmitted through the second fiber optic path switcher and returned along the original path will re-enter the second circulator and be transmitted to the beam combiner.

[0039] A beam combiner, located in the light-emitting direction of the first circulator and the second circulator, is used to couple the reflected light from the sample arm beam and the reference arm beam, and also to emit the coupled beam to the scanning acquisition imaging unit.

[0040] Secondly, the present invention provides a control method for a multifunctional ophthalmic femtosecond laser device, the method comprising:

[0041] The control optical path switching unit and the electronically controlled optical path switching mirror switch the multifunctional ophthalmic femtosecond device described in any of the above embodiments to the first OCT imaging and turn on the first visible light camera.

[0042] By observing the first visible light camera, the relative movement of the first objective lens and the target tissue is controlled so that the negative pressure ring is fixed on the target tissue, and the initial cutting area is determined.

[0043] The realignment is completed based on the two-dimensional or three-dimensional OCT imaging displayed by the fiber optic imaging unit and the imaging from the first visible light camera.

[0044] In one optional implementation, realignment is performed based on the two-dimensional or three-dimensional OCT image displayed by the fiber optic imaging unit and the image from the first visible light camera, including:

[0045] Based on the two-dimensional OCT imaging displayed by the fiber optic imaging unit, the first center coordinates of the first cutting area in the XOZ section and the second center coordinates in the YOZ section are determined.

[0046] Based on the first center coordinates and the second center coordinates, determine the point coordinates of the first cutting area in the XOY plane and display them in the first visible light camera;

[0047] The control point coordinates coincide with the indicator light point, completing the realignment.

[0048] In one optional implementation, realignment is performed based on the two-dimensional or three-dimensional OCT image displayed by the fiber optic imaging unit and the image from the first visible light camera, including:

[0049] Based on the three-dimensional OCT imaging displayed by the fiber optic imaging unit, the target tissue is reconstructed in three dimensions to generate a three-dimensional reconstructed image.

[0050] Based on the 3D reconstructed image, the coordinates of the interruption point of the first laser scan are determined and displayed in the first visible light camera;

[0051] Use the coordinates of the interruption point as the starting point for re-treatment.

[0052] In one alternative implementation, the method further includes:

[0053] The control optical path switching unit and the electronically controlled optical path switching mirror switch the multifunctional ophthalmic femtosecond device described in any of the above embodiments to the second OCT imaging and turn on the second visible light camera.

[0054] The target tissue after cutting was determined by observing the second visible light camera;

[0055] Determine the incision site for the target tissue using the eyepiece;

[0056] Based on the two-dimensional or three-dimensional OCT imaging displayed by the fiber optic imaging unit, the hierarchical state when the separation hook enters the target tissue can be determined.

[0057] The present invention has the following advantages:

[0058] The multifunctional femtosecond laser device for ophthalmology provided by this invention integrates optical coherence tomography (OCT) technology, adding more imaging information to the original visible light image. After loss due to negative pressure adsorption in the eyeball, the device can re-align the cut area using both visible light camera imaging (based on watermark retrieval) and OCT imaging, effectively improving re-alignment accuracy. Furthermore, based on the OCT imaging, the interlayer state of the separation hook or corneal lenticule can be more clearly visualized, preventing the separation hook from entering the wrong corneal lenticule layer.

[0059] In addition, by sharing the optical path, the switching between the first OCT imaging and the second OCT imaging can be realized, which can effectively simplify the optical path structure, save space and cost, and also effectively simplify the operation process and improve surgical efficiency.

[0060] The multifunctional ophthalmic femtosecond laser device provided in this invention adopts a "one sweeping light source, two sample arms" scheme. The sample arms use a galvanometer scanning method for OCT imaging. Each OCT sample arm corresponds to a reference arm. The first OCT sample arm works in conjunction with the first reference arm, and the second OCT sample arm works in conjunction with the second reference arm. The first OCT sample arm shares an optical lens and an optical planar scanner assembly with the femtosecond laser 3D scanning optical path. When imaging is required through the first sample arm (i.e., after aspiration loss, the first sample arm is used to navigate the realignment step under the negative pressure ring), the first fiber optic path switcher and the electrically controlled optical path switch mirror are opened to guide the sweeping laser after the 50:50 coupler into the first objective lens. Simultaneously, the second fiber optic path switcher is controlled to switch the reference arm optical path to the first reference arm to match the optical path and dispersion. When imaging is required through the second sample arm (i.e., when removing the lens under the microscope), the electronically controlled optical path switching mirror is turned off, and the first fiber optic path switcher is controlled to guide the swept laser into the second objective lens. Simultaneously, the second fiber optic path switcher is controlled to switch the reference arm optical path to the second reference arm to match the optical path and dispersion. In this way, the imaging mode of "one optical engine and two sample arms" can be achieved through the coordination of the first and second fiber optic path switches and the electronically controlled optical path switching mirror. Attached Figure Description

[0061] To more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0062] Figure 1 This is a structural block diagram of a multifunctional ophthalmic femtosecond laser device according to an embodiment of the present invention;

[0063] Figure 2 This is a structural block diagram of another interference loop according to an embodiment of the present invention;

[0064] Figure 3 This is a schematic flowchart of a multifunctional ophthalmic femtosecond laser method according to an embodiment of the present invention;

[0065] Figure 4 This is a flowchart illustrating another multifunctional femtosecond ophthalmic method according to an embodiment of the present invention;

[0066] Figure 5 This is a schematic diagram of an OCT cross-section according to an embodiment of the present invention;

[0067] Figure 6 This is a schematic diagram of a visible light image according to an embodiment of the present invention;

[0068] Figure 7 This is a flowchart illustrating another multifunctional femtosecond ophthalmic method according to an embodiment of the present invention;

[0069] Figure 8 This is a schematic diagram of the first cut area according to an embodiment of the present invention;

[0070] Figure 9 This is a schematic diagram of an OCT three-dimensional scanning cross-section according to an embodiment of the present invention;

[0071] Figure 10 This is a schematic diagram of the coordinates of the interruption point in the image according to an embodiment of the present invention;

[0072] Figure 11 This is a flowchart illustrating another multifunctional femtosecond ophthalmic method according to an embodiment of the present invention;

[0073] Figure 12 This is a schematic diagram of the OCT on the upper layer of the corneal lens according to an embodiment of the present invention;

[0074] Figure 13 This is a schematic diagram of the OCT of the lower layer of the corneal lens according to an embodiment of the present invention;

[0075] Figure Descriptions: 1-Scanning Imaging Module, 11-Fiber Optic Imaging Unit, 111-Sweeping Frequency Light Source, 112-Coupler, 1121-Beam Splitter, 1122-Attenuator, 1123-First Circulator, 1124-Second Circulator, 1125-Beam Combiner, 113-Scanning Acquisition Imaging Unit, 12-Optical Path Switching Unit, 121-First Fiber Optic Path Switcher, 122-Second Fiber Optic Path Switcher, 123-Collider, 1231-First Collimator, 1232-Second Collimator, 1233-Third Collimator, 1234-Fourth Collimator, 124-First High-reflection mirror, 125-Second high-reflection mirror, 13-Plane scanning galvanometer, 14-Reflecting mirror, 2-Femtosecond laser scanning module, 20-Laser parameter monitor, 21-Femtosecond laser, 22-Optical Z-axis scanner, 23-Electrically controlled optical path switching mirror, 24-Optical plane scanner, 25-First dichroic mirror, 26-First objective lens, 27-Negative pressure ring, 28-First visible light camera, 29-Laser diode, 3-Surgical microscope module, 31-Eyepiece, 32-Beam splitter, 33-Optical zoom lens, 34-Second dichroic mirror, 35-Second objective lens, 36-Second visible light camera. Detailed Implementation

[0076] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0077] This embodiment provides a multifunctional ophthalmic femtosecond laser device, such as... Figure 1 The diagram shown is a schematic of a multifunctional ophthalmic femtosecond laser device provided according to an embodiment of the present invention. The device includes: a scanning imaging module 1, a femtosecond laser scanning module 2, and a surgical microscope module 3, as detailed below.

[0078] The scanning imaging module 1 is used to emit a probe beam and perform OCT imaging. Among them, OCT (Optical Coherence Tomography) imaging includes two-dimensional OCT imaging or three-dimensional OCT imaging.

[0079] The femtosecond laser scanning module 2 is used to receive the probe beam and to irradiate the target tissue with the probe beam; the femtosecond laser scanning module 2 is also used to generate a femtosecond laser and focus the femtosecond laser onto the target tissue. The target tissue can be the cornea, eyeball, etc.

[0080] The surgical microscope module 3 is used to receive the probe beam and irradiate the target tissue with the probe beam; the surgical microscope module 3 is also used for microscope imaging.

[0081] The multifunctional ophthalmic femtosecond laser device provided in this embodiment integrates optical coherence tomography (OCT) technology, adding more imaging information to the original visible light image. After the loss of negative pressure adsorption in the eyeball, microscopic imaging can be performed using a surgical microscope module to easily locate the laser-cut area in the cornea. Then, OCT imaging is combined to re-align the cut area, which can effectively improve the re-alignment accuracy. After re-alignment, femtosecond laser is performed again, thus avoiding the problem of relatively limited imaging information.

[0082] In some optional implementations, the scanning imaging module 1 includes: an optical fiber imaging unit 11, an optical path switching unit 12, and a planar scanning galvanometer 13.

[0083] The fiber optic imaging unit 11 emits a probe beam and transmits it to the optical path switching unit 12. The fiber optic imaging unit 11 performs first OCT imaging when the femtosecond laser scanning module 2 receives the probe beam, and performs second OCT imaging when the surgical microscope module 3 receives the probe beam. The fiber optic imaging unit 11 can emit a probe beam of a preset wavelength, which can be 1300 nm or 1060 nm.

[0084] The optical path switching unit 12 is used to switch between the first OCT imaging and the second OCT imaging.

[0085] The planar scanning galvanometer 13 is positioned in the light output direction of the optical path switching unit 12.

[0086] In this embodiment, the scanning imaging module 1 is also referred to as the OCT module. Its function is to use tomographic imaging technology to observe the anterior segment image of the eyeball below the first objective lens 26 or the second objective lens 35. When the optical path switching unit 12 switches to the first OCT imaging, the first OCT sample arm operates, and the probe beam is emitted through the first OCT sample arm to the electrically controlled optical path switching mirror 23. The opening and closing of the electrically controlled optical path switching mirror 23 then controls whether the probe beam enters the optical plane scanner 24. At this time, observation can be performed through the first objective lens 26. When the optical path switching unit 12 switches to the second OCT imaging, the second OCT sample arm operates, and the probe beam is emitted through the second OCT sample arm to the plane scanning galvanometer 13, thereby entering the surgical microscope module 3. At this time, observation can be performed through the second objective lens 35.

[0087] The OCT image below the first objective lens 26 can be used to guide the surgeon in precise realignment during corneal re-treatment; the OCT image below the second objective lens 35 can be used to guide the surgeon in accurate visualization and layer separation during the corneal lenticule removal process. The device can be controlled to move in three dimensions to align with the eyeball.

[0088] In some alternative implementations, the femtosecond laser scanning module 2 includes a femtosecond laser 21, an optical Z-axis scanner 22, an electrically controlled optical path switching mirror 23, and an optical plane scanner 24 arranged sequentially.

[0089] The femtosecond laser 21 is used to generate a femtosecond laser with a preset wavelength, which can be 1030nm for corneal cutting. The electrically controlled optical path switching mirror 23 is used to receive the probe beam emitted by the optical path switching unit 12 and / or the femtosecond laser emitted after passing through the optical Z-axis scanner 22.

[0090] The electrically controlled optical path switching mirror 23 is turned on when the optical path switching unit 12 switches to the first OCT imaging, so as to transmit the received probe beam to the optical plane scanner 24; the electrically controlled optical path switching mirror 23 is turned off when the optical path switching unit 12 switches to the second OCT imaging.

[0091] The optical plane scanner 24 is used to irradiate the target tissue with the probe beam and / or focus the femtosecond laser onto the target tissue.

[0092] The function of the femtosecond laser scanning module 2 is to use the negative pressure ring 27 to adhere to the eyeball and perform corneal lenticule cutting to complete the refractive function. The optical Z-axis scanner 22 is used to change the laser beam divergence to achieve the depth of the laser focus in the Z direction in the cornea under the negative pressure ring 27; the optical plane scanner 24 is used to achieve the position of the laser focus in the XY plane in the cornea under the negative pressure ring 27.

[0093] When the femtosecond laser 21 is operating, the femtosecond laser can sequentially pass through the optical Z-axis scanner 22, the electrically controlled optical path switching mirror 23, and the optical plane scanner 24, and then be focused onto the target tissue to achieve treatments such as corneal resection. When the optical path switching unit 12 is in the first OCT imaging state, the electrically controlled optical path switching mirror 23 is turned on, and the probe beam is emitted through the first OCT sample arm to the electrically controlled optical path switching mirror 23, and then to the optical plane scanner 24, which illuminates the target tissue, thereby achieving OCT imaging. When the optical path switching unit 12 is in the second OCT imaging state, the electrically controlled optical path switching mirror 23 is turned off. At this time, the probe beam is emitted through the second OCT sample arm to the plane scanning galvanometer 13, and then enters the surgical microscope module 3.

[0094] The imaging method of "one optical engine and two sample arms" can be realized by the coordination of the electronically controlled optical path switching mirror 23 and the electronically controlled optical path switching mirror 23. The first sample arm shares the XY scanning optical engine component with the femtosecond laser scanning optical path. The femtosecond laser treatment function will not be affected after the electronically controlled switching mirror is turned off.

[0095] In some alternative implementations, the femtosecond laser scanning module 2 further includes:

[0096] The first dichroic mirror 25 is positioned in the light-emitting direction of the optical plane scanner 24 and is used to reflect the probe beam or femtosecond laser.

[0097] The first objective lens 26 is positioned in the first light-emitting direction of the first dichroic mirror 25 and is used to focus the probe beam and / or femtosecond laser onto the target tissue.

[0098] The negative pressure ring 27 is positioned between the first objective lens 26 and the target tissue to fix the target tissue.

[0099] The first visible light camera 28 is set in the second light-emitting direction of the first dichroic mirror 25 and is used to perform real-time imaging of the target tissue.

[0100] Laser diode 29 is used to generate an indicator light spot, which is used to indicate the target cutting point on the target tissue.

[0101] The first dichroic mirror 25 is used to reflect the visible light transmitted by the femtosecond laser. The first visible light camera 28, which can also be an infrared camera, can be used for real-time monitoring and imaging of the corneal surface under the negative pressure ring 27. The LD (laser diode 29) is used to emit a green indicator light to indicate the target point that the laser will cut. The first objective lens 26 is used to focus the femtosecond laser onto the corneal tissue under the negative pressure ring 27; the negative pressure ring 27 is used to attach the eyeball and fix the cornea.

[0102] Specifically, when the femtosecond laser 21 is working, the femtosecond laser can pass through the optical Z-axis scanner 22, the electronically controlled optical path switching mirror 23 and the optical plane scanner 24 in sequence. The femtosecond laser passing through the optical plane scanner 24 is reflected to the first objective lens 26 under the action of the first dichroic mirror 25, and then focused on the target tissue through the first objective lens 26 to achieve treatments such as corneal cutting.

[0103] When the optical path switching unit 12 switches to the first OCT imaging, the electronically controlled optical path switching mirror 23 is turned on. The detection beam is emitted through the first OCT sample arm to the electronically controlled optical path switching mirror 23, and then emitted to the optical plane scanner 24. The detection beam is irradiated to the target tissue under the action of the first dichroic mirror 25 and the first objective lens 26, thereby realizing OCT imaging.

[0104] At the same time, real-time imaging information of the target tissue can be observed through the first visible light camera 28.

[0105] In this embodiment, by using the electronically controlled optical path switching mirror 23 and its coordination, and by sharing the XY scanning optical mechanism with the first sample arm and the femtosecond laser scanning optical path, simultaneous imaging by the visible light camera and OCT can be achieved, effectively improving the realignment accuracy.

[0106] In some optional implementations, the surgical microscope module 3 is used to receive the reflected probe beam after being reflected by the planar scanning galvanometer 13 when switching from the first OCT imaging to the second OCT imaging, and to irradiate the target tissue with the reflected probe beam.

[0107] The function of the surgical microscope module 3 is to allow the surgeon to observe the cornea under the surgical microscope eyepiece 31 after the femtosecond laser corneal resection is completed, so as to cooperate with the two-dimensional or three-dimensional imaging of the fiber optic imaging unit 11 and remove the corneal lenticule using tools such as a separation hook.

[0108] The multifunctional femtosecond laser device for ophthalmology provided in this embodiment integrates optical coherence tomography (OCT) technology, adding more imaging information to the original visible light image. After loss of adsorption due to negative pressure in the eyeball, the device can re-align the cut area using OCT images, based on the watermark retrieval performed with a visible light camera, effectively improving re-alignment accuracy. Furthermore, the OCT images provide a more direct view of the interlayer state of the separation hook or corneal lenticule, preventing the separation hook from entering the wrong corneal lenticule layer.

[0109] Furthermore, by sharing the optical path, the switching between the first and second OCT imaging methods can be achieved, effectively simplifying the optical path structure, saving space and cost, and also simplifying the operation process and improving surgical efficiency. The entire device can be automatically controlled by a manual control box to achieve alignment with the patient's eyeball.

[0110] In some optional embodiments, the surgical microscope module 3 includes: an eyepiece 31, a beam splitter 32, an optical zoom lens 33, a second dichroic mirror 34, and a second objective lens 35 arranged sequentially; wherein the second dichroic mirror 34 is used to receive the reflected probe beam and irradiate the target tissue with the reflected probe beam.

[0111] The surgical microscope module 3 also includes a second visible light camera 36, ​​which is set in the light output direction of the beam splitter 32 for real-time imaging of the target tissue.

[0112] The surgical microscope includes an eyepiece 31, a second visible light camera 36, ​​a beam splitter 32, an optical zoom lens 33, a second dichroic mirror 34, and a second objective lens 35. The eyepiece 31, optical zoom lens 33, and second objective lens 35 form an optical microscopy system for observing the object under the second objective lens 35. The second dichroic mirror 34 is used to transmit visible light while reflecting a 1300nm probe beam.

[0113] In this embodiment, by combining the eyepiece 31 with OCT images, the interlayer state of the separation hook or corneal lens can be seen more intuitively, avoiding the problem of the separation hook entering the wrong corneal lens layer.

[0114] In some alternative embodiments, the fiber optic imaging unit 11 includes:

[0115] The frequency sweep light source 111 is used to generate a probe beam. The probe beam is emitted in the form of an optical fiber. In this embodiment, the frequency sweep light source 111 can be a 1300nm or 1060nm frequency sweep light source.

[0116] Coupler 112, positioned in the light-emitting direction of the swept frequency light source 111, is used to split the probe beam into a sample arm beam and a reference arm beam. In this embodiment, a 50:50 coupler 112 can be used, which is used to split the probe beam and form a re-interference condition. A Machzell interferometer can be used in this embodiment.

[0117] The scanning acquisition imaging unit 113 is used to perform OCT imaging based on the reflected light coherence of the sample arm beam and the reference arm beam. The scanning acquisition imaging unit 113 can employ OCT imaging technology to achieve high-resolution two-dimensional or three-dimensional imaging.

[0118] In some optional embodiments, the optical path switching unit 12 includes:

[0119] The first fiber optic path switcher 121 is used to switch the sample arm beam and also to realize the imaging switch between the first OCT imaging and the second OCT imaging. When the first fiber optic path switcher 121 is in the first OCT imaging mode, the sample arm beam is emitted to the electrically controlled optical path switching mirror 23 through the first collimator 1231. When the first fiber optic path switcher 121 is in the second OCT imaging mode, the sample arm beam is emitted to the plane scanning galvanometer 13 through the second collimator 1232.

[0120] The second fiber optic path switcher 122 is used to switch the reference arm beam and also to realize the imaging switch between the first OCT imaging and the second OCT imaging. When the first fiber optic path switcher 121 is in the first OCT imaging state, the reference arm beam is emitted to the first high-reflection mirror 124 through the third collimator 1233. When the first fiber optic path switcher 121 is in the second OCT imaging state, the reference arm beam is emitted to the second high-reflection mirror 125 through the fourth collimator 1234.

[0121] The scanning imaging module 1 includes a scanning acquisition imaging unit 113, a coupler 112, a first fiber optic path switcher 121, a second fiber optic path switcher 122, a first collimator 1231, a second collimator 1232, a third collimator 1233, a fourth collimator 1234, a first high-reflection mirror 124, a second high-reflection mirror 125, a planar scanning galvanometer 13, and a reflector 14.

[0122] The first fiber optic path switcher 121 and the second fiber optic path switcher 122 are used to switch the optical signal between the two output fibers using an electronic control method; the collimator is used to collimate the scanning laser transmitted through the fiber optic cable into spatial light; the first high-reflection mirror 124 and the second high-reflection mirror 125 are used to return the frequency-scanning laser along its original path; the planar scanning galvanometer 13 is used to perform row and column scanning of the frequency-scanning laser in space; and the reflector 14 is used to guide the beam after the planar scanning galvanometer 13 into the surgical microscope.

[0123] The multifunctional ophthalmic femtosecond laser device provided in this embodiment adopts a "one sweeping light source, two sample arms" scheme. The sample arms use a galvanometer scanning method for OCT imaging. Each OCT sample arm corresponds to a reference arm. The first OCT sample arm works in conjunction with the first reference arm, and the second OCT sample arm works in conjunction with the second reference arm. The first OCT sample arm shares an optical lens and an optical plane scanner 24 assembly with the femtosecond laser 3D scanning optical path. When imaging via the first sample arm is required (i.e., after aspiration loss, the first sample arm is used to navigate the realignment step under the negative pressure ring 27), the first fiber optic path switcher 121 and the electrically controlled optical path switch mirror 23 are opened to guide the sweeping laser after the 50:50 coupler 112 into the first objective lens 26. Simultaneously, the second fiber optic path switcher 122 switches the reference arm optical path to the first reference arm to match the optical path and dispersion. When imaging is required through the second sample arm (i.e., when removing the lens under the microscope), the electronically controlled optical path switching mirror 23 is turned off, and the first fiber optic path switcher 121 is controlled to guide the swept laser into the second objective lens 35. At the same time, the second fiber optic path switcher 122 is controlled to switch the reference arm optical path to the second reference arm to match the optical path and dispersion. In this way, the imaging mode of "one optical engine and two sample arms" can be realized through the coordination of the first fiber optic path switcher 121, the second fiber optic path switcher 122, and the electronically controlled optical path switching mirror 23.

[0124] Thanks to the tomographic resolution of OCT, even if the air bubbles in the initial ablation zone completely disappear, the traces left by laser cutting are still clearly visible under OCT. It's worth mentioning that the OCT design not only addresses existing clinical pain points but also provides more possibilities for functional expansion of this product. Besides its use in the repositioning process after aspiration loss during femtosecond LASIK surgery, the OCT sample arm can also be used for preoperative anterior segment measurement and surgical parameter planning in femtosecond cataract surgery. The specific control method is as follows: After the eyeball is attracted using the negative pressure ring 27, the first OCT sample arm is used to perform three-dimensional imaging of the anterior segment of the eyeball to measure corneal thickness, anterior chamber depth, and the position and depth of the anterior and posterior surfaces of the lens. Then, the measured OCT anterior segment image is used to plan the specific location for the next femtosecond cataract surgery ablation. In this function, the negative pressure ring 27 and the eyeball remain stably connected during both the OCT measurement process and the femtosecond laser ablation of the lens. Therefore, the reference coordinates of the lens relative to the negative pressure ring 27 remain constant during OCT measurement and femtosecond laser ablation.

[0125] In addition to guiding lens retrieval during femtosecond LASIK surgery, the OCT second sample arm can also be used for testing and evaluation during inlay implantation for hyperopia correction. During the gel inlay implantation for hyperopia correction, the thickness and shape of the inlay implant can be displayed in real time through the OCT second sample arm (i.e., the OCT function of the surgical microscope), which is used to evaluate the degree of hyperopia correction in real time and guide the surgery.

[0126] In this embodiment, an OCT configuration consisting of one sweep frequency light source, two sample arms, and two reference arms can achieve two OCT imaging sites by sharing the same sweep frequency light source. This can solve both the problem of accurate realignment after aspiration loss and the problem of incorrect layer entry when removing lenses. After aspiration loss, the OCT scanning optical path for realignment can be switched by an electronically controlled optical path switching mirror to share the optical path with the XY scanning optical path of the femtosecond laser.

[0127] Reference Figure 2 As shown, in some alternative embodiments, coupler 112 includes:

[0128] Beam splitter 1121 is positioned in the light output direction of swept frequency light source 111 and is used to generate sample arm beam and reference arm beam.

[0129] Attenuator 1122 is set in the reference output direction of beam splitter 1121 and is used to receive the reference arm beam and adjust the intensity of optical power.

[0130] The first circulator 1123 is located in the sample light output direction of the beam splitter 1121 and is used to receive the sample arm beam. The sample arm beam that passes through the first circulator 1123 is emitted to the first fiber optic path switcher 121. The optical signal that is transmitted through the first fiber optic path switcher 121 and returns along the original path will re-enter the first circulator 1123 and be transmitted to the beam combiner 1125.

[0131] The second circulator 1124 is located in the light output direction of the attenuator 1122. The light beam emitted through the reference arm of the second circulator 1124 is sent to the second fiber optic path switcher 122. The light signal transmitted through the second fiber optic path switcher 122 and returned along the original path will re-enter the second circulator 1124 and be transmitted to the beam combiner 1125.

[0132] The beam combiner 1125 is positioned in the light-emitting direction of the first circulator 1123 and the second circulator 1124. It is used to couple the reflected light of the sample arm beam and the reference arm beam, and also to emit the coupled beam to the scanning acquisition imaging unit 113.

[0133] This embodiment uses a Michelson interferometer, therefore, it includes two additional circulators to form a Michelson interferometric loop. Compared to a Machzell interferometer, the Michelson interferometer has the following advantages: higher power utilization efficiency for the interference signal light, resulting in a better signal-to-noise ratio for the acquired imaging signal; and the interference signal light does not return to the swept light source along its original path, thus not affecting the output performance of the probe beam.

[0134] In some alternative implementations, the femtosecond laser scanning module 2 further includes:

[0135] The laser parameter monitor 20 is connected to the output end of the femtosecond laser 21 and is used to monitor the laser parameters of the femtosecond laser. The laser parameter monitor 20 is used to monitor parameters such as power and energy of the femtosecond laser, which can ensure the stability and consistency of the femtosecond laser output.

[0136] This embodiment also provides a control method for a multifunctional ophthalmic femtosecond laser device, which can be executed by the multifunctional ophthalmic femtosecond laser device in any of the above embodiments. Figure 3 This is a flowchart of a control method for a multifunctional ophthalmic femtosecond laser device according to an embodiment of the present invention, such as... Figure 3 As shown, the process includes the following steps:

[0137] Step S101: Control the optical path switching unit 12 and the electronically controlled optical path switching mirror 23 to switch the multifunctional ophthalmic femtosecond device in any of the above embodiments to the first OCT imaging and turn on the first visible light camera 28.

[0138] Step S102: By observing the first visible light camera 28, control the first objective lens 26 to move relative to the target tissue, so that the negative pressure ring 27 is fixed on the target tissue, and determine the first cutting area;

[0139] Step S103: Based on the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the fiber optic imaging unit 11 and the imaging in the first visible light camera 28, the realignment is completed.

[0140] In this embodiment, the image navigation technology control method of OCT in the multifunctional ophthalmic femtosecond device can be divided into the following two types: one is the OCT navigation method in the realignment process after refractive surgery loss of aspiration, and the other is the OCT navigation method in the lens retrieval process. Among them, the OCT realignment process after refractive surgery loss of aspiration also includes two-dimensional navigation method and three-dimensional navigation method.

[0141] In this embodiment, by using the scanning imaging module 1 and the femtosecond laser scanning module 2 in the multifunctional ophthalmic femtosecond device, and integrating OCT images based on a visible light camera, precise realignment after refractive surgery aspiration loss can be achieved.

[0142] This embodiment also provides a control method for a multifunctional ophthalmic femtosecond laser device, which can be executed by the multifunctional ophthalmic femtosecond laser device in any of the above embodiments. It is suitable for two-dimensional realignment after loss of negative pressure adsorption during ophthalmic refractive surgery. (Refer to...) Figure 4 As shown, the process includes the following steps:

[0143] Step S201: Control the optical path switching unit 12 and the electronically controlled optical path switching mirror 23 to switch the multifunctional ophthalmic femtosecond device in any of the above embodiments to the first OCT imaging and turn on the first visible light camera 28.

[0144] Step S202: By observing the first visible light camera 28, control the first objective lens 26 to move with the target tissue, so that the negative pressure ring 27 is fixed on the target tissue, and determine the first cutting area;

[0145] Step S203: Based on the two-dimensional OCT imaging displayed by the fiber optic imaging unit 11, determine the first center coordinates of the first cutting area in the XOZ section and the second center coordinates in the YOZ section.

[0146] Step S204: Determine the point coordinates of the first cutting area in the XOY plane based on the first center coordinates and the second center coordinates, and display them in the first visible light camera 28;

[0147] Step S205: The coordinates of the control point coincide with the indicator light point, completing the realignment.

[0148] OCT has the ability to directly acquire depth information in a single scan. The cross-scan mode involves cyclically scanning two orthogonal crosshairs in the X and Y directions to acquire tomographic images of the sections containing these crosshairs. The navigation process is detailed below:

[0149] (1) Background conditions: When negative pressure is lost during femtosecond laser corneal ablation, the surgeon judges that re-treatment can be started immediately.

[0150] (2) The control system switches the OCT mode to the cross scan mode of the first sample arm and turns on the first visible light camera 28. Observe the first visible light camera 28 and control the movement to basically align the eyeball with the negative pressure ring 27.

[0151] (3) The surgeon observes the image from the first visible light camera (28) to find the approximate location of the initial cutting area. The surgeon then visually observes the OCT cross-scan image. The laser cutting trajectory of the initial cutting area in the OCT image is a curve composed of tiny white bubbles, as shown below. Figure 5 As shown, the first center coordinates X0 and the second center coordinates Y0 of the initial cutting zone in the XOZ and YOZ sections were analyzed using the cutting zone feature information from the OCT cross-section diagram.

[0152] The specific analysis method is as follows: Find the coordinates of the left and right endpoints X1 / X2 and Y1 / Y2 of the corneal cutting zone trajectory (the curve composed of white bubbles) in the XOZ and YOZ cross-sectional images respectively, X0=(X1-X2) / 2, Y0=(Y1-Y2) / 2.

[0153] (4) The XOZ and YOZ sections of the OCT image have been pre-registered with the coordinate axes of the XOY section image captured by the first visible light camera 28. The coordinates (X0, Y0) of the points in the XOY plane formed by X0 and Y0 are virtually displayed in real time on the left side of the first visible light camera 28 image (shown as blue dots), as shown. Figure 6As shown.

[0154] The coordinate axis registration method is as follows: simultaneously image objects such as metal plates with cross lines by using the cross scan mode of the first visible light camera 28 and the first sample arm of the OCT, and align the center point of the OCT imaging area and the center point of the imaging area of ​​the first visible light camera 28 with the center of the cross lines to complete the registration.

[0155] (5) The doctor views the camera image, operates the machine to align with the eyeball, and completes the manual realignment by aligning the blue dot with the green dot. The green dot is the indicator light emitted by the LD (laser diode 29) to indicate the position to be cut.

[0156] (6) The green and blue dots can be observed in the first visible light camera 28. The relative distance between them can be obtained using software recognition methods. When the distance is less than 0.1 mm, they are considered to be aligned. When the green and blue dots appear simultaneously in the image, they can be aligned automatically. The multifunctional ophthalmic femtosecond device can achieve three-dimensional relative movement with the eyeball under controlled motion.

[0157] In this embodiment, the OCT scanning speed is fast and the interface information can be displayed in real time to guide the doctor to control the first objective lens 26 to complete the realignment in real time.

[0158] This embodiment also provides a control method for a multifunctional ophthalmic femtosecond laser device, which can be executed by the multifunctional ophthalmic femtosecond laser device in any of the above embodiments. It is applicable to three-dimensional realignment after loss of negative pressure adsorption during another ophthalmic refractive surgery. (Refer to...) Figure 7 As shown, the process includes the following steps:

[0159] Step S301: Control the optical path switching unit 12 and the electronically controlled optical path switching mirror 23 to switch the multifunctional ophthalmic femtosecond device in any of the above embodiments to the first OCT imaging and turn on the first visible light camera 28.

[0160] Step S302: By observing the first visible light camera 28, control the first objective lens 26 to move relative to the target tissue, so that the negative pressure ring 27 is fixed on the target tissue, and determine the first cutting area;

[0161] Step S303: Based on the three-dimensional OCT imaging displayed by the fiber optic imaging unit 11, the target tissue is reconstructed in three dimensions to generate a three-dimensional reconstructed image.

[0162] Step S304: Based on the 3D reconstructed image, determine the coordinates of the interruption point of the first laser scan and display them in the first visible light camera 28;

[0163] Step S305: Use the coordinates of the interruption point as the starting point for retreatment.

[0164] The navigation process is detailed below:

[0165] (1) Background conditions: Negative pressure is lost during femtosecond laser corneal ablation, and the surgeon judges that re-treatment can be started immediately.

[0166] (2) The control system switches the OCT mode to the cross-scan mode of the first sample arm, and at the same time turns on the first visible light camera 28. It controls the movement of the first objective lens 26 (i.e., the entire device moves as shown) to align the eyeball with the negative pressure ring 27 to find the first cutting area. The image is shown on the right. Figure 8 As shown. The search process is as follows: The surgeon observes the image from the first visible light camera 28 to find the approximate location of the initial cutting area, and then observes the OCT cross scan image with the naked eye. The laser cutting trajectory of the initial cutting area in the OCT image is a curve composed of tiny white bubbles.

[0167] (3) The doctor observes the OCT cross scan image, controls the first objective lens 26 to move the cutting area in the left and right direction to the position of the image basically in the center, and then starts the negative pressure to suction the eyeball to complete the initial alignment.

[0168] (4) Open the OCT 3D scanning mode, the image is as follows Figure 9 As shown.

[0169] (5) Quickly complete the OCT 3D scanning and reconstruction of the anterior segment, and use the algorithm to directly analyze the interruption points X0, Y0, and Z0 of the first scan from the 3D image. The specific search idea is to use features (surfaces composed of white highlighted lines) in the 3D reconstructed space to find the cutting area, and then analyze and calculate the coordinates of the interruption points along the cutting process edge, such as... Figure 10 As shown.

[0170] (6) The computer controls the focus of the femtosecond laser through software. When the treatment is repeated, the scanning starts from the interruption point X0, Y0, Z0, so as to achieve a perfect continuation of the treatment and the first ablation.

[0171] In this embodiment, the three-dimensional OCT scan is slow, but it can directly provide the coordinates of the three-dimensional breakpoints, making the treatment results more accurate.

[0172] Reference Figure 11 As shown, in some optional implementations, the method further includes:

[0173] Step S401: Control the optical path switching unit 12 and the electronically controlled optical path switching mirror 23 to switch the multifunctional ophthalmic femtosecond device in any of the above embodiments to the second OCT imaging and turn on the second visible light camera 36.

[0174] Step S402: Determine the cut target tissue by observing the second visible light camera 36;

[0175] Step S403: Determine the incision opening for the target tissue through eyepiece 31;

[0176] Step S404: Determine the hierarchical state when the separation hook enters the target tissue based on the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the fiber optic imaging unit 11.

[0177] The navigation method used in OCT during lens retrieval is as follows:

[0178] (1) Place the eye after femtosecond laser ablation under the objective lens of the surgical microscope, turn on the cross scan mode of the second camera of the surgical microscope module 3 and the second sample arm of the OCT, and find the image of the laser-cut area in the cornea.

[0179] (2) The surgeon observes the corneal incision location through the eyepiece 31 of the microscope (which is the same as the second camera view) so that the dissection hook can be used to enter the corneal incision to carry out corneal lenticule separation.

[0180] (3) The surgeon observes the OCT image to determine the layer status of the separation hook entering the corneal lenticule.

[0181] (4) After confirming the separation hook is in the correct state via OCT screen (e.g., upper layer, such as...), Figure 12 (as shown), so that it can be peeled off.

[0182] (5) After completing the separation of one layer, another corneal layer (such as the lower layer) is separated using a separation hook with the assistance of OCT images, such as... Figure 13 As shown.

[0183] (6) After all layers are separated, the corneal lens is removed using tools such as lens tweezers under the OCT image or camera view.

[0184] In this embodiment, by combining the eyepiece 31 with OCT images, the interlayer state of the separation hook or corneal lens can be seen more intuitively, avoiding the problem of the separation hook entering the wrong corneal lens layer.

[0185] Although embodiments of the invention have been described in conjunction with the accompanying drawings, those skilled in the art can make various modifications and variations without departing from the spirit and scope of the invention, and such modifications and variations all fall within the scope defined by the appended claims.

Claims

1. A multifunctional ophthalmic femtosecond laser device, characterized in that, The device includes: A scanning imaging module (1) is used to emit a probe beam and perform OCT imaging; the scanning imaging module (1) includes: a fiber optic imaging unit (11), an optical path switching unit (12), and a planar scanning galvanometer (13); the fiber optic imaging unit (11) is used to emit the probe beam and transmit it to the optical path switching unit (12); the fiber optic imaging unit (11) is used to perform a first OCT imaging when the femtosecond laser scanning module (2) receives the probe beam, and to perform a second OCT imaging when the surgical microscope module (3) receives the probe beam; the optical path switching unit (12) is used to realize the imaging switching between the first OCT imaging and the second OCT imaging; the planar scanning galvanometer (13) is arranged in the light emission direction of the optical path switching unit (12); The femtosecond laser scanning module (2) is used to receive the probe beam and to irradiate the target tissue with the probe beam; the femtosecond laser scanning module (2) is also used to generate a femtosecond laser and focus the femtosecond laser onto the target tissue; The surgical microscope module (3) is used to receive the probe beam and irradiate the target tissue with the probe beam; the surgical microscope module (3) is also used for microscope imaging.

2. The apparatus according to claim 1, characterized in that, The femtosecond laser scanning module (2) includes a femtosecond laser (21), an optical Z-axis scanner (22), an electronically controlled optical path switching mirror (23), and an optical plane scanner (24) arranged in sequence. The femtosecond laser (21) is used to generate femtosecond laser, and the electrically controlled optical path switching mirror (23) is used to receive the probe beam emitted by the optical path switching unit (12) and / or the femtosecond laser emitted after passing through the optical Z-axis scanner (22). The electrically controlled optical path switching mirror (23) is turned on when the optical path switching unit (12) switches to the first OCT imaging, so as to transmit the received detection beam to the optical plane scanner (24); the electrically controlled optical path switching mirror (23) is turned off when the optical path switching unit (12) switches to the second OCT imaging; The optical plane scanner (24) is used to irradiate the detection beam onto the target tissue and / or focus the femtosecond laser onto the target tissue; The femtosecond laser scanning module (2) also includes: A first dichroic mirror (25) is disposed in the light-emitting direction of the optical plane scanner (24) for reflecting the probe beam or the femtosecond laser. The first objective lens (26) is set in the first light-emitting direction of the first dichroic mirror (25) and is used to focus the probe beam and / or the femtosecond laser into the target tissue; A negative pressure ring (27) is provided between the first objective lens (26) and the target tissue to fix the target tissue; The first visible light camera (28) is set in the second light-emitting direction of the first dichroic mirror (25) and is used to perform real-time imaging of the target tissue; A laser diode (29) is used to generate an indicator light spot, which is used to indicate a target cutting point on the target tissue.

3. The apparatus according to claim 1, characterized in that, The surgical microscope module (3) is used to receive the reflected detection beam after being reflected by the planar scanning galvanometer (13) when the first OCT imaging is switched to the second OCT imaging, and to irradiate the target tissue with the reflected detection beam; The surgical microscope module (3) includes: an eyepiece (31), a beam splitter (32), an optical zoom lens (33), a second dichroic mirror (34), and a second objective lens (35) arranged in sequence; wherein, the second dichroic mirror (34) is used to receive the reflected detection beam and irradiate the target tissue with the reflected detection beam; The surgical microscope module (3) also includes a second visible light camera (36), which is set in the light output direction of the beam splitter (32) for real-time imaging of the target tissue.

4. The apparatus according to claim 2, characterized in that, The fiber optic imaging unit (11) includes: A frequency-sweeping light source (111) is used to generate the detection beam, which emits light via an optical fiber. A coupler (112) is disposed in the light output direction of the swept frequency light source (111) and is used to split the probe beam into a sample arm beam and a reference arm beam. The scanning acquisition imaging unit (113) is used to perform OCT imaging based on the reflection of the sample arm beam and the reference arm beam after coherence. The optical path switching unit (12) includes: A first fiber optic path switcher (121) is used to switch the sample arm beam to achieve imaging switching between the first OCT imaging and the second OCT imaging. When the first fiber optic path switcher (121) is in the first OCT imaging state, the sample arm beam is emitted to the electrically controlled optical path switching mirror (23) through the first collimator (1231). When the first fiber optic path switcher (121) is in the second OCT imaging state, the sample arm beam is emitted to the planar scanning galvanometer (13) through the second collimator (1232). The second fiber optic path switcher (122) is used to switch the reference arm beam to realize the imaging switch between the first OCT imaging and the second OCT imaging; when the first fiber optic path switcher (121) is in the first OCT imaging, the reference arm beam is emitted to the first high-reflection mirror (124) through the third collimator (1233); when the first fiber optic path switcher (121) is in the second OCT imaging, the reference arm beam is emitted to the second high-reflection mirror (125) through the fourth collimator (1234).

5. The apparatus according to claim 4, characterized in that, The coupler (112) includes: A beam splitter (1121) is disposed in the light output direction of the swept frequency light source (111) and is used to generate the sample arm beam and the reference arm beam. An attenuator (1122) is disposed in the reference light output direction of the beam splitter (1121) for receiving the reference arm beam and adjusting the optical power intensity. The first circulator (1123) is located in the sample light output direction of the beam splitter (1121) and is used to receive the sample arm beam. The sample arm beam that passes through the first circulator (1123) is emitted to the first fiber optic path switcher (121). The optical signal that passes through the first fiber optic path switcher (121) and returns along the original path will re-enter the first circulator (1123) and be transmitted to the beam combiner (1125). The second circulator (1124) is located in the light output direction of the attenuator (1122). The light beam emitted through the reference arm of the second circulator (1124) is sent to the second fiber optic path switcher (122). The light signal transmitted through the second fiber optic path switcher (122) and returned along the original path will re-enter the second circulator (1124) and be transmitted to the beam combiner (1125). A beam combiner (1125) is disposed in the light-emitting direction of the first circulator (1123) and the second circulator (1124) for coupling the reflected light of the sample arm beam and the reference arm beam, and for emitting the coupled beam to the scanning acquisition imaging unit (113).

Images