Multifunctional ophthalmic femtosecond device and use method

Abstract

The invention relates to the technical field of femtosecond laser, and discloses a multifunctional ophthalmology femtosecond device and a use method, and the device comprises a scanning imaging module which is used for emitting a detection light beam and carrying out OCT imaging; the femtosecond laser scanning module is used for receiving the detection light beam and irradiating the detection light beam to the target tissue; the femtosecond laser scanning module is also used for generating femtosecond laser and focusing the femtosecond laser to the target tissue; the operating microscope module is used for receiving the detection light beam and irradiating the detection light beam to a target tissue; the operating microscope module is also used for carrying out microscope imaging. According to the method, the optical coherence tomography technology is fused, more imaging information is added on the basis of an original visible light image, the re-alignment precision can be effectively improved, and the problem that a separation hook enters a wrong corneal lens layer is avoided.

Description

Technical Field

[0001] The present invention relates to the field of femtosecond laser technology, and in particular to a multifunctional ophthalmic femtosecond device and a use method thereof. Background Art

[0002] Femtosecond laser is an extremely short pulse laser, commonly used in ophthalmic refractive surgery, femtosecond cataract surgery, etc. During the operation, a negative pressure adsorption device is often used to fix the eyeball to ensure accurate cutting of the cornea or lens. During the femtosecond laser scanning process, the negative pressure adsorption of the eyeball may be lost due to factors such as the patient's involuntary eye movement, causing the operation to be interrupted or delayed.

[0003] For ophthalmic refractive surgery, the common treatment methods currently include elective redo or re-treatment. Elective re-treatment will greatly affect the patient's experience, and re-treatment is generally completed by using a visible light camera to align the watermark of the first cutting area. However, the boundary of the watermark area composed of bubbles left in the first cutting area is very fuzzy and easy to disappear, resulting in a very low re-alignment accuracy, with an error of about 1mm. In clinical practice, the lateral alignment accuracy should be less than 200um to avoid the problem of eccentric cutting. Therefore, the method of re-alignment using bubble watermarks under the camera is very likely to cause eccentric secondary cutting and affect the patient's postoperative visual quality. In addition, during femtosecond refractive surgery, the corneal stroma is usually cut twice, the first time at a slightly shallower position, and the second time at a slightly deeper position. After cutting, a thin corneal tissue will be produced between the two layers, which needs to be removed, that is, the lens removal process. Currently, the common practice is to perform the operation under the eyepiece of a surgical microscope. The common practice is for the doctor to judge the level entry state by feel and the planar top view of the optical microscope objective lens. However, this can easily lead to the separation hook entering the wrong corneal lens layer, resulting in difficulty or even failure in lens removal.

[0004] Therefore, there is an urgent need for a multifunctional all-in-one ophthalmic femtosecond device that can not only ensure accurate positioning during treatment but also provide more imaging information under an optical microscope. Summary of the invention

[0005] In view of this, the present invention provides a multifunctional ophthalmic femtosecond device and a method of use to solve the problems of low re-alignment accuracy and relatively single imaging information of the femtosecond device in the prior art.

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

[0007] A scanning imaging module, used for emitting a detection beam and performing OCT imaging;

[0008] A femtosecond laser scanning module is used to receive a detection beam and irradiate the detection beam to a target tissue; the femtosecond laser scanning module is also used to generate a femtosecond laser and focus the femtosecond laser to the target tissue;

[0009] The surgical microscope module is used to receive the detection beam and irradiate the detection beam to the target tissue; the surgical microscope module is also used to perform microscope imaging.

[0010] In an optional embodiment, the scanning imaging module includes: an optical fiber light-emitting imaging unit, an optical path switching unit, and a planar scanning galvanometer;

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

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

[0013] The plane scanning galvanometer is arranged in the light emitting direction of the optical path switching unit.

[0014] In an optional embodiment, 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, which are arranged in sequence;

[0015] The femtosecond laser is used to generate femtosecond laser, and the electrically controlled optical path switching mirror is used to receive the detection 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 is switched to the first OCT imaging to transmit the received detection beam to the optical plane scanner; the electrically controlled optical path switching mirror is turned off when the optical path switching unit is switched to the second OCT imaging;

[0017] The optical plane scanner is used to irradiate the probe beam to the target tissue and / or focus the femtosecond laser to the target tissue;

[0018] Femtosecond laser scanning module, also includes:

[0019] A first dichroic mirror is arranged in the light-outgoing direction of the optical plane scanner and is used to reflect the detection beam or the femtosecond laser;

[0020] A first objective lens, arranged in a first light-emitting direction of the first dichroic mirror, for focusing the detection beam and / or the femtosecond laser into the target tissue;

[0021] A negative pressure ring is disposed between the first objective lens and the target tissue and is used to fix the target tissue;

[0022] A first visible light camera, arranged in the second light-emitting direction of the first dichroic mirror, for real-time imaging of the target tissue;

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

[0024] In an optional embodiment, the surgical microscope module is used to receive the reflected detection beam after being reflected by the planar scanning galvanometer when the first OCT imaging is switched to the second OCT imaging, and irradiate the reflected detection beam to the target tissue;

[0025] The surgical microscope module includes: an eyepiece, a beam splitter, an optical magnification changer, a second dichroic mirror and a second objective lens which are arranged in sequence; wherein the second dichroic mirror is used to receive a reflected detection beam and irradiate the reflected detection beam to a target tissue;

[0026] The surgical microscope module also includes a second visible light camera, which is arranged in the light emitting direction of the beam splitter and is used for real-time imaging of the target tissue.

[0027] In an optional implementation, the optical fiber light-emitting imaging unit includes:

[0028] A swept frequency light source is used to generate a detection light beam, and the detection light beam is emitted in the form of an optical fiber;

[0029] A coupler is arranged in the light emitting direction of the frequency sweeping light source and is used to divide the detection beam into a sample arm beam and a reference arm beam;

[0030] A scanning acquisition imaging unit is used to perform OCT imaging based on the coherence of the reflected light from the sample arm beam and the reference arm beam;

[0031] Optical path switching unit, comprising:

[0032] A first optical fiber optical path switcher is used to switch the sample arm light beam to realize imaging switching between the first OCT imaging and the second OCT imaging; when the first optical fiber optical path switcher is in the first OCT imaging, the sample arm light beam is emitted to the electrically controlled optical path switching mirror through the first collimator; when the first optical fiber optical path switcher is in the second OCT imaging, the sample arm light beam is emitted to the planar scanning galvanometer through the second collimator;

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

[0034] In an optional embodiment, the coupler comprises:

[0035] A beam splitter is arranged in the light emitting direction of the swept light source and is used to generate a sample arm beam and a reference arm beam;

[0036] An attenuator is arranged in the reference light output direction of the beam splitter, and is used to receive the reference arm light beam and adjust the light power intensity;

[0037] The first circulator is arranged in the sample light emitting direction of the beam splitter, and is used to receive the sample arm light beam.

[0038] The sample arm light beam of the first circulator is emitted to the first optical fiber optical path switcher, and the optical signal transmitted through the first optical fiber optical path switcher and returned along the original path will enter the first circulator again and be transmitted to the beam combiner;

[0039] A second circulator is arranged in the light output direction of the attenuator. The reference arm light beam passing through the second circulator is emitted to the second optical fiber optical path switcher. The optical signal transmitted through the second optical fiber optical path switcher and returned along the original path will enter the second circulator again and be transmitted to the beam combiner.

[0040] The beam combiner is arranged in the light emitting direction of the first circulator and the second circulator, and is used to couple the reflected light of the sample arm beam and the reference arm beam, and is also used to emit the coupled light beam to the scanning acquisition imaging unit.

[0041] In a second aspect, the present invention provides a method for using a multifunctional ophthalmic femtosecond device, the method comprising:

[0042] Controlling the optical path switching unit and the electrically controlled optical path switching mirror to switch the multifunctional ophthalmic femtosecond device described in any one of the above embodiments to the first OCT imaging, and turning on the first visible light camera;

[0043] By observing the first visible light camera, the first objective lens and the target tissue are controlled to move relative to each other so that the negative pressure ring is fixed on the target tissue, thereby determining the first cutting area;

[0044] The realignment is completed according to the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit and the imaging in the first visible light camera.

[0045] In an optional implementation, the re-alignment is completed according to the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit and the imaging in the first visible light camera, including:

[0046] Determine the first center coordinates of the first cutting area in the XOZ section and the second center coordinates of the first cutting area in the YOZ section according to the two-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit;

[0047] Determine the point coordinates of the first cutting area in the XOY plane according to the first center coordinates and the second center coordinates, and display them in the first visible light camera;

[0048] The coordinates of the control point coincide with the indicator light spot, completing the realignment.

[0049] In an optional implementation, the re-alignment is completed according to the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit and the imaging in the first visible light camera, including:

[0050] According to the three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit, the target tissue is three-dimensionally reconstructed to generate a three-dimensional reconstructed image;

[0051] According to the three-dimensional reconstructed image, the coordinates of the interruption point of the first laser scan are determined and displayed in the first visible light camera;

[0052] The coordinates of the interruption point are used as the starting point for re-treatment.

[0053] In an optional embodiment, the method further includes:

[0054] Controlling the optical path switching unit and the electrically controlled optical path switching mirror to switch the multifunctional ophthalmic femtosecond device described in any one of the above embodiments to the second OCT imaging, and turning on the second visible light camera;

[0055] Determine the target tissue after cutting by observing the second visible light camera;

[0056] Determine the incision opening of the target tissue through the eyepiece;

[0057] According to the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit, the layer state of the separation hook when entering the target tissue is determined.

[0058] The present invention has the following advantages:

[0059] The multifunctional ophthalmic femtosecond device provided by the present invention integrates optical coherence tomography technology and adds more imaging information on the basis of the original visible light image. After the negative pressure adsorption of the eyeball is lost, the re-alignment of the cutting area can be achieved by combining the OCT image with the watermark search of the cutting area using a visible light camera, which can effectively improve the re-alignment accuracy. In addition, based on the OCT image, the interlayer state of the separation hook or corneal lens can be more intuitively seen to avoid the problem of the separation hook entering the wrong corneal lens layer.

[0060] In addition, by sharing the optical path, the mutual 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 effectively simplify the operation process and improve surgical efficiency.

[0061] The multifunctional ophthalmic femtosecond device provided in the present invention adopts the scheme of "one swept frequency light source, two sample arms" as a whole. The sample arm adopts a galvanometer scanning method for OCT imaging. Each OCT sample arm corresponds to a reference arm. The first OCT sample arm cooperates with the first reference arm, and the second OCT sample arm cooperates with the second reference arm. The OCT first sample arm and the femtosecond laser three-dimensional scanning optical path share the optical lens and the optical plane scanner assembly. When imaging is required through the first sample arm (i.e., after loss of absorption, the first sample arm is used to navigate the re-alignment step under the negative pressure ring), the first optical fiber optical path switcher and the electrically controlled optical path switching mirror are controlled to open, and the swept frequency laser after the 50:50 coupler is introduced into the first objective lens. At the same time, the second optical fiber optical 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 taking a lens under a microscope), turn off the electrically controlled optical path switching mirror and control the first optical fiber optical path switcher to direct the frequency-sweeping laser into the second objective lens, and at the same time control the second optical fiber optical path switcher to switch the reference arm optical path to the second reference arm to match the optical path and dispersion. In this way, the imaging method of "one light engine with two sample arms" can be realized through the coordination of the first optical fiber optical path switcher, the second optical fiber optical path switcher, and the electrically controlled optical path switching mirror. BRIEF DESCRIPTION OF THE DRAWINGS

[0062] In order to more clearly illustrate the specific implementation methods of the present invention or the technical solutions in the prior art, the drawings required for use in the specific implementation methods or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are some implementation methods of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0063] Figure 1 is a structural block diagram of a multifunctional ophthalmic femtosecond device according to an embodiment of the present invention;

[0064] Figure 2 is a structural block diagram of another interference loop according to an embodiment of the present invention;

[0065] Figure 3 is a schematic flow chart of a multifunctional ophthalmic femtosecond method according to an embodiment of the present invention;

[0066] Figure 4 is a schematic flow chart of another multifunctional ophthalmic femtosecond method according to an embodiment of the present invention;

[0067] Figure 5 is a schematic diagram of an OCT cross-scan section according to an embodiment of the present invention;

[0068] Figure 6 is a schematic diagram of a visible light image according to an embodiment of the present invention;

[0069] Figure 7 is a schematic flow chart of another multifunctional ophthalmic femtosecond method according to an embodiment of the present invention;

[0070] Figure 8 is a schematic diagram of a screen of a first cutting area according to an embodiment of the present invention;

[0071] Fig. 9 is a schematic diagram of an OCT three-dimensional scanning cross section according to an embodiment of the present invention;

[0072] Fig.10 is a schematic diagram of the coordinates of the interruption points in the picture according to an embodiment of the present invention;

[0073] Fig.11 is a schematic flow chart of another multifunctional ophthalmic femtosecond method according to an embodiment of the present invention;

[0074] Fig.12 is an OCT schematic diagram of the upper layer of a corneal lens according to an embodiment of the present invention;

[0075] Fig.13 is an OCT schematic diagram of the lower layer of the corneal lens according to an embodiment of the present invention;

[0076] Description of the drawings: 1-scanning imaging module, 11-fiber light emitting imaging unit, 111-sweeping 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 optical fiber optical path switcher, 122-second optical fiber optical path switcher, 123-collimator, 1231-first collimator, 1232-second collimator, 1233-third collimator, 1234-fourth collimator, 124-first High-reflective mirror, 125-second high-reflective 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 light 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 magnification changer, 34-second dichroic mirror, 35-second objective lens, 36-second visible light camera. DETAILED DESCRIPTION

[0077] In order to make the purpose, technical solution and advantages of the embodiments of the present invention clearer, the technical solution in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are 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 those skilled in the art without creative work are within the scope of protection of the present invention.

[0078] In this embodiment, a multifunctional ophthalmic femtosecond device is provided, such as Figure 1 , which is a schematic diagram of a multifunctional ophthalmic femtosecond device according to an embodiment of the present invention, the device comprises: a scanning imaging module 1, a femtosecond laser scanning module 2 and a surgical microscope module 3, as follows.

[0079] The scanning imaging module 1 is used to emit a detection beam and perform OCT imaging, wherein OCT (Optical Coherence Tomography) imaging includes two-dimensional OCT imaging or three-dimensional OCT imaging.

[0080] The femtosecond laser scanning module 2 is used to receive the detection beam and irradiate the detection beam to the target tissue; the femtosecond laser scanning module 2 is also used to generate femtosecond laser and focus the femtosecond laser to the target tissue. The target tissue may be the cornea, the eyeball, etc.

[0081] The surgical microscope module 3 is used to receive the detection light beam and irradiate the detection light beam to the target tissue; the surgical microscope module 3 is also used to perform microscope imaging.

[0082] The multifunctional ophthalmic femtosecond device provided in this embodiment integrates optical coherence tomography technology, and adds more imaging information on the basis of the original visible light image. After the negative pressure adsorption of the eyeball is lost, the surgical microscope module can be used for microscope imaging to facilitate finding the image of the laser cutting area in the cornea. Then, the re-alignment of the cutting area is achieved in combination with OCT imaging, which can effectively improve the accuracy of re-alignment. After the re-alignment is completed, the femtosecond laser is performed again, thereby avoiding the problem of relatively single imaging information.

[0083] In some optional implementations, the scanning imaging module 1 includes: an optical fiber light-emitting imaging unit 11 , an optical path switching unit 12 , and a planar scanning galvanometer 13 .

[0084] The optical fiber light-emitting imaging unit 11 is used to emit a detection beam and transmit it to the optical path switching unit 12. The optical fiber light-emitting imaging unit 11 is used to perform a first OCT imaging when the femtosecond laser scanning module 2 receives the detection beam, and to perform a second OCT imaging when the surgical microscope module 3 receives the detection beam. The optical fiber light-emitting imaging unit 11 can emit a detection beam of a preset wavelength, which can be 1300nm or 1060nm.

[0085] The optical path switching unit 12 is used to implement imaging switching between the first OCT imaging and the second OCT imaging.

[0086] The plane scanning galvanometer 13 is arranged in the light emitting direction of the optical path switching unit 12 .

[0087] The scanning imaging module 1 is also referred to as an OCT module in this embodiment, and its function is to use tomographic imaging technology to observe the image of the anterior segment of the eyeball below the first objective lens 26 or below the second objective lens 35. When the optical path switching unit 12 switches to the first OCT imaging, the OCT first sample arm works, and the detection beam is emitted to the electrically controlled optical path switching mirror 23 through the OCT first sample arm, and then the opening and closing of the electrically controlled optical path switching mirror 23 controls whether the detection beam enters the optical plane scanner 24. At this time, it can be observed through the first objective lens 26. When the optical path switching unit 12 switches to the second OCT imaging, the OCT second sample arm works, and the detection beam is emitted to the plane scanning galvanometer 13 through the OCT second sample arm, thereby entering the surgical microscope module 3. At this time, it can be observed through the second objective lens 35.

[0088] The OCT image below the first objective lens 26 can be used to guide the operator to accurately re-align the cornea during re-treatment; the OCT image below the second objective lens 35 can be used to guide the operator to accurately visualize the layer separation during the corneal lens removal process. The device can be controlled to translate in three dimensions as a whole to achieve docking with the eyeball.

[0089] In some optional embodiments, 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 , which are arranged in sequence.

[0090] The femtosecond laser 21 is used to generate a femtosecond laser of a preset wavelength, which may be 1030 nm for corneal cutting. The electrically controlled optical path switching mirror 23 is used to receive the detection beam emitted by the optical path switching unit 12 and / or the femtosecond laser emitted after being transmitted through the optical Z-axis scanner 22.

[0091] The electrically controlled optical path switching mirror 23 is turned on when the optical path switching unit 12 switches to the first OCT imaging 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.

[0092] The optical plane scanner 24 is used to irradiate the probe beam onto the target tissue and / or focus the femtosecond laser onto the target tissue.

[0093] The function of the femtosecond laser scanning module 2 is to use the negative pressure ring 27 to absorb the eyeball to achieve corneal lens cutting to complete the refractive function. The optical Z-axis scanner 22 is used to change the divergence of the laser beam to achieve the Z-direction depth of the laser focus 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.

[0094] When the femtosecond laser 21 is working, 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 focus on the target tissue to achieve treatments such as corneal cutting. When the optical path switching unit 12 is in the first OCT imaging, the electrically controlled optical path switching mirror 23 is turned on, and the detection beam is emitted to the electrically controlled optical path switching mirror 23 through the OCT first sample arm, and then emitted to the optical plane scanner 24, and irradiated to the target tissue through the optical plane scanner 24, thereby achieving OCT imaging. When the optical path switching unit 12 is in the second OCT imaging, the electrically controlled optical path switching mirror 23 is turned off. At this time, the detection beam is emitted to the plane scanning galvanometer 13 through the OCT second sample arm, thereby entering the surgical microscope module 3.

[0095] The imaging mode of "one light engine and two sample arms" can be realized through the cooperation of the electrically-controlled optical path switching mirror 23 and the electrically-controlled optical path switching mirror 23. The first sample arm and the femtosecond laser scanning optical path share the XY scanning optical machine component, and the femtosecond laser treatment function will not be affected after controlling the electrically-controlled switching mirror to be turned off.

[0096] In some optional embodiments, the femtosecond laser scanning module 2 further includes:

[0097] The first dichroic mirror 25 is disposed in the light-emitting direction of the optical plane scanner 24 and is used to reflect the detection beam or the femtosecond laser.

[0098] The first objective lens 26 is arranged in the first light emitting direction of the first dichroic mirror 25, and is used to focus the detection beam and / or the femtosecond laser into the target tissue.

[0099] A negative pressure ring 27 is disposed between the first objective lens 26 and the target tissue and is used to fix the target tissue;

[0100] The first visible light camera 28 is disposed in the second light emitting direction of the first dichroic mirror 25 and is used for real-time imaging of the target tissue.

[0101] The laser diode 29 is used to generate an indication light spot, and the indication light spot is used to indicate a target cutting point on the target tissue.

[0102] The first dichroic mirror 25 is used to reflect the visible light transmitted by the femtosecond laser. The first visible light camera 28 can also be an infrared camera, which can be used to monitor and image the corneal surface under the negative pressure ring 27 in real time. The LD (laser diode 29) is used to emit a green indicator light spot to indicate the target point where the laser will cut. The first objective lens 26 is used to focus the femtosecond laser on the corneal tissue under the negative pressure ring 27; the negative pressure ring 27 is used to absorb the eyeball to fix the cornea.

[0103] Specifically, when the femtosecond laser 21 is working, the femtosecond laser can pass through the optical Z-axis scanner 22, the electrically-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 to the target tissue through the first objective lens 26 to achieve corneal cutting and other treatments.

[0104] When the optical path switching unit 12 switches to the first OCT imaging, the electrically-controlled optical path switching mirror 23 is turned on, and the detection beam is emitted to the electrically-controlled optical path switching mirror 23 through the OCT first sample arm, 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.

[0105] At the same time, real-time imaging information of the target tissue can be observed through the first visible light camera 28 .

[0106] In this embodiment, by means of the electrically controlled optical path switching mirror 23 and the coordination of the electrically controlled optical path switching mirror 23, the first sample arm and the femtosecond laser scanning optical path share the XY scanning optical machine component, so that the visible light camera and OCT can be imaged simultaneously, effectively improving the re-alignment accuracy.

[0107] In some optional embodiments, the surgical microscope module 3 is used to receive the reflected detection light beam reflected by the plane scanning galvanometer 13 and irradiate the reflected detection light beam to the target tissue when the first OCT imaging is switched to the second OCT imaging.

[0108] The function of the surgical microscope module 3 is to allow the surgeon to observe the cornea under the surgical microscope eyepiece 31 after completing the femtosecond laser corneal cutting, and to use tools such as separation hooks to remove the corneal lens in conjunction with the two-dimensional or three-dimensional imaging of the fiber optic light-emitting imaging unit 11.

[0109] The multifunctional ophthalmic femtosecond device provided in this embodiment integrates optical coherence tomography technology, and adds more imaging information on the basis of the original visible light image. After the negative pressure adsorption of the eyeball is lost, the re-alignment of the cutting area can be achieved by combining the OCT image with the watermark search of the cutting area using a visible light camera, which can effectively improve the re-alignment accuracy. In addition, based on the OCT image, the interlayer state of the separation hook or corneal lens can be more intuitively seen to avoid the problem of the separation hook entering the wrong corneal lens layer.

[0110] In addition, by sharing the optical path, the first OCT imaging and the second OCT imaging can be switched to each other, which can effectively simplify the optical path structure, save space and cost, and effectively simplify the operation process and improve surgical efficiency. The entire device can be automatically controlled by a manual control box to achieve alignment with the patient's eyeball.

[0111] In some optional embodiments, the surgical microscope module 3 includes: an eyepiece 31, a beam splitter 32, an optical magnification changer 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 reflected detection beam to the target tissue.

[0112] The surgical microscope module 3 further includes a second visible light camera 36 , which is arranged in the light emitting direction of the beam splitter 32 and is used for real-time imaging of the target tissue.

[0113] The surgical microscope comprises an eyepiece 31, a second visible light camera 36, ​​a beam splitter 32, an optical magnification changer 33, a second dichroic mirror 34 and a second objective lens 35. The eyepiece 31, the optical magnification changer 33 and the second objective lens 35 form an optical microscope system for observing the object to be measured under the second objective lens 35. The second dichroic mirror 34 is used to reflect a 1300 nm detection beam through visible light.

[0114] In this embodiment, based on the eyepiece 31 and combined with the OCT image, the interlayer state of the separation hook or the corneal lens can be more intuitively seen, thereby avoiding the problem of the separation hook entering the wrong layer of the corneal lens.

[0115] In some optional embodiments, the optical fiber light-emitting imaging unit 11 includes:

[0116] The swept frequency light source 111 is used to generate a detection light beam, and the detection light beam is emitted in the form of an optical fiber. In this embodiment, the swept frequency light source 111 can be a 1300nm or 1060nm swept frequency light source.

[0117] The coupler 112 is arranged in the light emitting direction of the swept frequency light source 111, and is used to split the detection beam into a sample arm beam and a reference arm beam. In this embodiment, a 50:50 coupler 112 can be used, and the 50:50 coupler 112 is used to split the detection beam and form a second interference condition. In this embodiment, a Mach-Zehnder interferometer can be used.

[0118] The scanning acquisition imaging unit 113 is used to perform OCT imaging based on the coherence of the reflected light from the sample arm beam and the reference arm beam. The scanning acquisition imaging unit 113 can use OCT imaging technology to achieve high-resolution two-dimensional or three-dimensional imaging.

[0119] In some optional implementations, the optical path switching unit 12 includes:

[0120] The first optical fiber optical path switch 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 optical fiber optical path switch 121 is in the first OCT imaging, the sample arm beam is emitted to the electrically controlled optical path switching mirror 23 through the first collimator 1231; when the first optical fiber optical path switch 121 is in the second OCT imaging, the sample arm beam is emitted to the plane scanning galvanometer 13 through the second collimator 1232;

[0121] The second optical fiber optical path switch 122 is used to switch the reference arm beam and also to realize imaging switching between the first OCT imaging and the second OCT imaging; when the first optical fiber optical path switch 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 optical fiber optical path switch 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.

[0122] The scanning imaging module 1 includes a scanning acquisition imaging unit 113, a coupler 112, a first optical fiber optical path switch 121, a second optical fiber optical path switch 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.

[0123] The first optical fiber optical path switch 121 and the second optical fiber optical path switch 122 are used to realize the switching of optical signals in two output optical fibers by means of electrical control; the collimator is used to collimate the scanning laser transmitted by the optical fiber and output it as spatial light; the first high-reflection mirror 124 and the second high-reflection mirror 125 are used to return the scanning laser to its original path; the plane scanning galvanometer 13 is used to realize spatial row and column scanning of the scanning laser; the reflector 14 is used to guide the light beam after the plane scanning galvanometer 13 into the surgical microscope.

[0124] The multifunctional ophthalmic femtosecond device provided in this embodiment adopts the scheme of "one swept frequency light source, two sample arms" as a whole. The sample arm adopts a galvanometer scanning method for OCT imaging. Each OCT sample arm corresponds to a reference arm. The first OCT sample arm cooperates with the first reference arm, and the second OCT sample arm cooperates with the second reference arm. The OCT first sample arm and the femtosecond laser three-dimensional scanning optical path share the optical lens and optical plane scanner 24 components. When imaging is required through the first sample arm (that is, after loss of absorption, the first sample arm is used to navigate the re-alignment step under the negative pressure ring 27), the first optical fiber optical path switcher 121 and the electrically controlled optical path switching mirror 23 are controlled to open, and the swept frequency laser after the 50:50 coupler 112 is introduced into the first objective lens 26, and the second optical fiber optical path switcher 122 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 taking a lens under a microscope), the electrically controlled optical path switching mirror 23 is turned off and the first optical fiber optical path switch 121 is controlled to guide the frequency sweeping laser into the second objective lens 35, while the second optical fiber optical path switch 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 light engine with two sample arms" can be realized through the coordination of the first optical fiber optical path switch 121, the second optical fiber optical path switch 122 and the electrically controlled optical path switching mirror 23.

[0125] Thanks to the tomographic resolution ability of OCT, even if the bubbles in the first cutting area completely disappear, the traces of laser cutting are clearly visible under OCT. It is worth mentioning that the design of OCT not only solves the existing clinical pain points, but also provides more possibilities for the functional expansion of this product. In addition to being used in the re-alignment process after aspiration loss in all-femtosecond surgery, the OCT sample arm can also be used for preoperative anterior segment measurement and surgical parameter planning in femtosecond cataract surgery. The specific method of use is: after using the negative pressure ring 27 to adsorb the eyeball, first use the OCT first sample arm to perform three-dimensional imaging of the anterior segment of the eyeball to measure the corneal thickness, anterior chamber depth, and the position and depth of the anterior and posterior surfaces of the lens. Then use the measured OCT anterior segment image to plan the specific location that needs to be cut in the next femtosecond cataract surgery. In this function, the negative pressure ring 27 and the eyeball are always in a stable connection state during the OCT measurement process and the femtosecond laser cutting process. Therefore, the reference coordinates of the lens relative to the negative pressure ring 27 during OCT measurement and femtosecond laser cutting are fixed.

[0126] In addition to navigating lens removal during all-femtosecond surgery, the OCT second sample arm can also be used for testing and evaluation of inlay implantation for hyperopia correction. During the process of gel inlay implantation for hyperopia correction, the OCT second sample arm (i.e., the OCT function of the surgical microscope) can display the thickness and morphology of the inlay implant in real time, which is used to evaluate the degree of hyperopia correction in real time and guide the operation.

[0127] In this embodiment, a set of swept light sources, two sample arms and two reference arms of the OCT configuration can realize OCT imaging at two locations by sharing the same swept light source, which can be used to solve the problem of accurate re-alignment after loss of absorption and the problem of easy misplacement of the lens. The OCT scanning optical path for re-alignment after loss of absorption can be switched by an electrically controlled optical path switching mirror to realize the sharing of the optical path with the XY scanning optical path of the femtosecond laser.

[0128] Reference Figure 2 As shown, in some optional embodiments, the coupler 112 includes:

[0129] The beam splitter 1121 is disposed in the light emitting direction of the swept-frequency light source 111 and is used to generate a sample arm beam and a reference arm beam.

[0130] The attenuator 1122 is arranged in the reference light output direction of the beam splitter 1121, and is used to receive the reference arm light beam and adjust the light power.

[0131] The first circulator 1123 is arranged in the sample light output direction of the beam splitter 1121, and is used to receive the sample arm light beam. The sample arm light beam passing through the first circulator 1123 is emitted to the first optical fiber optical path switcher 121. The optical signal transmitted through the first optical fiber optical path switcher 121 and returned along the original route will enter the first circulator 1123 again and be transmitted to the combiner 1125.

[0132] The second circulator 1124 is arranged in the light output direction of the attenuator 1122. The reference arm light beam passing through the second circulator 1124 is emitted to the second optical fiber optical path switch 122. The optical signal transmitted through the second optical fiber optical path switch 122 and returned along the original route will enter the second circulator 1124 again and be transmitted to the combiner 1125.

[0133] The beam combiner 1125 is arranged in the light emitting direction of the first circulator 1123 and the second circulator 1124 , and is used to couple the reflected light of the sample arm beam and the reference arm beam, and is also used to emit the coupled light beam to the scanning acquisition imaging unit 113 .

[0134] This embodiment adopts a Michelson interferometer, so this embodiment has two more circulators to form a Michelson interference loop. The Michelson interferometer has the following advantages over the Mach-Zehnder interferometer structure: the power utilization efficiency of the interference signal light is higher, so the signal-to-noise ratio of the obtained imaging signal is relatively better; the interference signal light will not return to the swept frequency light source and affect the output performance of the detection beam.

[0135] In some optional embodiments, the femtosecond laser scanning module 2 further includes:

[0136] The laser parameter monitor 20 is connected to the light 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 the power and energy of the femtosecond laser and ensure the stability and consistency of the femtosecond laser output.

[0137] In this embodiment, a method for using a multifunctional ophthalmic femtosecond device is also provided, which can be performed by the multifunctional ophthalmic femtosecond device in any of the above embodiments. Figure 3 is a flow chart of a method for using a multifunctional ophthalmic femtosecond device according to an embodiment of the present invention. Figure 3 As shown, the process includes the following steps:

[0138] Step S101, controlling the optical path switching unit 12 and the electrically controlled optical path switching mirror 23, switching the multifunctional ophthalmic femtosecond device in any of the above embodiments to the first OCT imaging, and turning on the first visible light camera 28;

[0139] Step S102, by observing the first visible light camera 28, controlling 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 determining the first cutting area;

[0140] Step S103 , completing realignment according to the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit 11 and the imaging in the first visible light camera 28 .

[0141] In this embodiment, the method of using the OCT image navigation technology in the multifunctional ophthalmic femtosecond device can be divided into the following two types: one is the navigation method of OCT during the re-alignment process after aspiration loss in refractive surgery, and the other is the navigation method of OCT during the lens removal process, wherein the OCT re-alignment process after aspiration loss in refractive surgery also includes a two-dimensional navigation method and a three-dimensional navigation method.

[0142] In this embodiment, by using the scanning imaging module 1 and the femtosecond laser scanning module 2 in the multifunctional ophthalmic femtosecond device, the OCT image is integrated on the basis of the visible light camera to achieve accurate re-alignment after aspiration during refractive surgery.

[0143] This embodiment also provides a method for using a multifunctional ophthalmic femtosecond device, which can be performed by the multifunctional ophthalmic femtosecond device in any of the above embodiments, and is suitable for two-dimensional re-alignment after the negative pressure adsorption of the eyeball is lost in ophthalmic refractive surgery, referring to Figure 4 As shown, the process includes the following steps:

[0144] Step S201, controlling the optical path switching unit 12 and the electrically controlled optical path switching mirror 23, switching the multifunctional ophthalmic femtosecond device in any of the above embodiments to the first OCT imaging, and turning on the first visible light camera 28;

[0145] Step S202, by observing the first visible light camera 28, controlling the first objective lens 26 and the target tissue to move so that the negative pressure ring 27 is fixed on the target tissue, and determining the first cutting area;

[0146] Step S203, determining the first center coordinates of the first cutting area in the XOZ section and the second center coordinates of the first cutting area in the YOZ section according to the two-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit 11;

[0147] Step S204, determining the point coordinates of the first cutting area in the XOY plane according to the first center coordinates and the second center coordinates, and displaying them in the first visible light camera 28;

[0148] Step S205: the coordinates of the control point coincide with the indicating light spot, and realignment is completed.

[0149] OCT has the ability to directly obtain depth information in the depth direction with a single scan. The cross scan mode is to cyclically scan two orthogonal cross lines in the XY direction to obtain the tomographic image of the section where the two cross lines are located. The navigation process is detailed as follows:

[0150] (1) Background conditions: When negative pressure is lost during corneal ablation by femtosecond laser, the surgeon determines that re-treatment can be started immediately.

[0151] (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 , observes the first visible light camera 28 , and controls the movement to basically align the eyeball with the negative pressure ring 27 .

[0152] (3) The surgeon observes the image of the first visible light camera 28 to find the approximate position of the first cutting area, and observes the OCT cross scan image with the naked eye. The laser cutting track of the first cutting area under the OCT image is a curve composed of white tiny bubbles, such as Figure 5 The first center coordinate X0 and the second center coordinate Y0 of the first cutting area in the XOZ and YOZ sections are analyzed respectively by analyzing the cutting area feature information in the OCT cross-scan section.

[0153] The specific analysis method is: find the left and right endpoint coordinates X1 / X2 and Y1 / Y2 of the corneal cutting area trajectory (the curve composed of white bubbles) in the XOZ and YOZ cross-sectional images respectively, X0 = (X1-X2) / 2, Y0 = (Y1-Y2) / 2.

[0154] (4) The XOZ and YOZ sections of the OCT image have been pre-aligned with the coordinate axes of the XOY section image captured by the first visible light camera 28. The point coordinates (X0, Y0) in the XOY plane composed of X0 and Y0 are displayed virtually in real time on the left side of the first visible light camera 28 (indicated by the blue dot), as shown in FIG. Figure 6shown.

[0155] The coordinate axis registration method is: use the cross scanning mode of the first visible light camera 28 and the OCT first sample arm to simultaneously image objects such as metal plates with cross marks, and align the center point of the OCT imaging area and the center point of the first visible light camera 28 imaging area with the center of the cross marks to complete the registration.

[0156] (5) The doctor watches the camera image, operates the machine to align with the eyeball, and aligns the blue dot with the green dot to complete the manual re-alignment. The green dot is the indicator light emitted by the LD (laser diode 29) to indicate the position to be cut.

[0157] (6) The green dot and the blue dot can be displayed and observed in the first visible light camera 28. The relative distance between the two can be obtained by software recognition method. When the distance is less than 0.1 mm, it is considered that the two are aligned. When the green dot and the blue dot appear in the picture at the same time, the alignment can be achieved by automatic alignment. The multifunctional ophthalmic femtosecond device can realize three-dimensional relative movement with the eyeball by controlled movement.

[0158] 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 in real time to complete the realignment.

[0159] This embodiment also provides a method for using a multifunctional ophthalmic femtosecond device, which can be performed by the multifunctional ophthalmic femtosecond device in any of the above embodiments, and is suitable for three-dimensional repositioning after the negative pressure adsorption of the eyeball is lost in another ophthalmic refractive surgery, referring to Figure 7 As shown, the process includes the following steps:

[0160] Step S301, controlling the optical path switching unit 12 and the electrically controlled optical path switching mirror 23, switching the multifunctional ophthalmic femtosecond device in any of the above embodiments to the first OCT imaging, and turning on the first visible light camera 28;

[0161] Step S302, by observing the first visible light camera 28, controlling 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 determining the first cutting area;

[0162] Step S303, performing three-dimensional reconstruction of the target tissue according to the three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit 11, and generating a three-dimensional reconstructed image;

[0163] Step S304, determining the coordinates of the interruption point of the first laser scan according to the three-dimensional reconstructed image, and displaying them in the first visible light camera 28;

[0164] Step S305, taking the coordinates of the interruption point as the starting point of re-treatment.

[0165] The navigation process is detailed as follows:

[0166] (1) Background conditions: When the negative pressure is lost during corneal ablation by femtosecond laser, the surgeon decides that re-treatment can be started immediately.

[0167] (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, controls the movement of the first objective lens 26 (i.e., the entire device moves), docks the eyeball with the negative pressure ring 27, and finds the first cutting area. The picture is as shown on the right. Figure 8 The search process is as follows: the operator observes the image of the first visible light camera 28 to find the approximate position of the first cutting area, and observes the OCT cross scan image with the naked eye. The laser cutting track of the first cutting area under the OCT image is a curve composed of white tiny bubbles.

[0168] (3) The doctor observes the OCT cross-scan image, controls the first objective lens 26 to move the cutting area to a substantially central position of the image in the left-right direction, and then activates negative pressure to suck the eyeball to complete preliminary alignment.

[0169] (4) Open the OCT 3D scanning mode. The screen is as follows Fig. 9 shown.

[0170] (5) Quickly complete the OCT 3D scanning and reconstruction of the anterior segment of the eye, and use the algorithm to directly analyze the interruption points X0, Y0, and Z0 of the first scan from the 3D image. The specific idea of ​​​​the search is to use the features (the surface 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, such as Fig.10 shown.

[0171] (6) The computer controls the focus of the femtosecond laser through software, and the scanning starts from the interruption point X0, Y0, Z0 during re-treatment, achieving a perfect connection between the re-treatment and the first cutting.

[0172] In this embodiment, the three-dimensional OCT scanning speed is slow, but the three-dimensional breakpoint coordinates can be directly given, making the re-treatment results more accurate.

[0173] Reference Fig.11 As shown, in some optional embodiments, the method further includes:

[0174] Step S401, controlling the optical path switching unit 12 and the electrically controlled optical path switching mirror 23, switching the multifunctional ophthalmic femtosecond device in any of the above embodiments to the second OCT imaging, and turning on the second visible light camera 36;

[0175] Step S402, determining the target tissue after cutting by observing the second visible light camera 36;

[0176] Step S403, determining the incision opening of the target tissue through the eyepiece 31;

[0177] Step S404 , determining the layer state of the separation hook when entering the target tissue according to the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit 11 .

[0178] The OCT navigation method during lens removal is as follows:

[0179] (1) The eye after femtosecond laser cutting is placed under the objective lens of the surgical microscope, and the second camera of the surgical microscope module 3 and the cross scan mode of the second sample arm of the OCT are turned on to find the image of the laser cutting area in the cornea.

[0180] (2) The operator observes the corneal incision position through the eyepiece 31 of the microscope (the same as the second camera screen) so as to use the separation hook to enter the corneal incision to carry out corneal lens separation.

[0181] (3) The surgeon observes the OCT image to determine the level of the separation hook entering the corneal lens.

[0182] (4) After confirming that the separation hook is in the correct state through the OCT screen (for example, the upper layer, such as Fig.12 as shown) for easy peeling.

[0183] (5) After completing the separation of one layer, the separation hook is used to separate another corneal layer (such as the lower layer) with the assistance of OCT images. Fig.13 shown.

[0184] (6) After all layers are separated, use tools such as lens forceps to remove the corneal lens under the OCT image or camera screen.

[0185] In this embodiment, based on the eyepiece 31 and combined with the OCT image, the interlayer state of the separation hook or the corneal lens can be more intuitively seen, thereby avoiding the problem of the separation hook entering the wrong layer of the corneal lens.

[0186] Although the embodiments of the present invention have been described in conjunction with the accompanying drawings, those skilled in the art may make various modifications and variations without departing from the spirit and scope of the present invention, and such modifications and variations are all within the scope defined by the appended claims.

Claims

1. A multifunctional ophthalmic femtosecond device, characterized in that: The device comprises: A scanning imaging module (1), used for emitting a detection beam and performing OCT imaging; A femtosecond laser scanning module (2) is used to receive the detection light beam and to irradiate the detection light beam onto the target tissue; the femtosecond laser scanning module (2) is also used to generate a femtosecond laser and to focus the femtosecond laser onto the target tissue; The surgical microscope module (3) is used to receive the detection light beam and irradiate the detection light beam onto the target tissue; the surgical microscope module (3) is also used to perform microscope imaging.

2. The device according to claim 1, characterized in that The scanning imaging module (1) comprises: an optical fiber light-emitting imaging unit (11), an optical path switching unit (12), and a planar scanning galvanometer (13); The optical fiber light-emitting imaging unit (11) is used to emit the detection light beam and transmit it to the optical path switching unit (12); the optical fiber light-emitting imaging unit (11) is used to perform a first OCT imaging when the femtosecond laser scanning module (2) receives the detection light beam, and to perform a second OCT imaging when the surgical microscope module (3) receives the detection light beam; The optical path switching unit (12) is used to realize imaging switching between the first OCT imaging and the second OCT imaging; The plane scanning galvanometer (13) is arranged in the light emitting direction of the light path switching unit (12).

3. The device according to claim 2, characterized in that The femtosecond laser scanning module (2) comprises a femtosecond laser (21), an optical Z-axis scanner (22), an electrically controlled optical path switching mirror (23), and an optical plane scanner (24) which are 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 detection light beam emitted by the optical path switching unit (12) and / or the femtosecond laser emitted after being transmitted 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 light 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 to the target tissue and / or focus the femtosecond laser to the target tissue; The femtosecond laser scanning module (2) further comprises: A first dichroic mirror (25) is arranged in the light emitting direction of the optical plane scanner (24) and is used to reflect the detection light beam or the femtosecond laser; A first objective lens (26), arranged in a first light-emitting direction of the first dichroic mirror (25), and used for focusing the detection beam and / or the femtosecond laser into the target tissue; a negative pressure ring (27), arranged between the first objective lens (26) and the target tissue, and used for fixing the target tissue; A first visible light camera (28), arranged in the second light emitting direction of the first dichroic mirror (25), and used for real-time imaging of the target tissue; A laser diode (29) is used to generate an indication light spot, wherein the indication light spot is used to indicate a target cutting point on the target tissue.

4. The device according to claim 2, characterized in that The surgical microscope module (3) is used for receiving the reflected detection light beam reflected by the planar scanning galvanometer (13) and irradiating the reflected detection light beam to the target tissue when the first OCT imaging is switched to the second OCT imaging; The surgical microscope module (3) comprises: an eyepiece (31), a beam splitter (32), an optical magnification changer (33), a second dichroic mirror (34) and a second objective lens (35) which are arranged in sequence; wherein the second dichroic mirror (34) is used to receive the reflected detection light beam and irradiate the reflected detection light beam onto the target tissue; The surgical microscope module (3) further comprises a second visible light camera (36), which is arranged in the light emitting direction of the beam splitter (32) and is used for real-time imaging of the target tissue.

5. The device according to claim 3, characterized in that The optical fiber light-emitting imaging unit (11) comprises: A swept frequency light source (111) is used to generate the detection light beam, and the detection light beam is emitted in the form of an optical fiber; A coupler (112), arranged in the light emitting direction of the frequency sweeping light source (111), and used for dividing the detection light beam into a sample arm light beam and a reference arm light beam; A scanning acquisition imaging unit (113) is used to perform OCT imaging based on the coherence of the reflected light from the sample arm light beam and the reference arm light beam; The optical path switching unit (12) comprises: A first optical fiber optical path switcher (121) is used to switch the sample arm light beam to realize imaging switching between the first OCT imaging and the second OCT imaging; when the first optical fiber optical path switcher (121) is in the first OCT imaging, the sample arm light beam is emitted to the electrically controlled optical path switching mirror (23) through a first collimator (1231); when the first optical fiber optical path switcher (121) is in the second OCT imaging, the sample arm light beam is emitted to the planar scanning galvanometer (13) through a second collimator (1232); The second optical fiber optical path switch (122) is used to switch the reference arm light beam to realize imaging switching between the first OCT imaging and the second OCT imaging; when the first optical fiber optical path switch (121) is in the first OCT imaging, the reference arm light beam is emitted to the first high-reflection mirror (124) through the third collimator (1233); when the first optical fiber optical path switch (121) is in the second OCT imaging, the reference arm light beam is emitted to the second high-reflection mirror (125) through the fourth collimator (1234).

6. The device according to claim 5, characterized in that The coupler (112) comprises: A beam splitter (1121) is arranged in the light emitting direction of the swept frequency light source (111) and is used to generate the sample arm light beam and the reference arm light beam; An attenuator (1122), arranged in the reference light output direction of the beam splitter (1121), used for receiving the reference arm light beam and adjusting the light power intensity; A first circulator (1123) is arranged in the sample light emitting direction of the beam splitter (1121) and is used to receive the sample arm light beam. The sample arm light beam passing through the first circulator (1123) is emitted to the first optical fiber optical path switcher (121). The optical signal transmitted through the first optical fiber optical path switcher (121) and returned along the original path will enter the first circulator (1123) again and be transmitted to the beam combiner (1125); A second circulator (1124) is arranged in the light output direction of the attenuator (1122), and the reference arm light beam passing through the second circulator (1124) is emitted to the second optical fiber optical path switch (122), and the optical signal transmitted through the second optical fiber optical path switch (122) and returned along the original path will enter the second circulator (1124) again and be transmitted to the beam combiner (1125); A beam combiner (1125) is arranged in the light emitting direction of the first circulator (1123) and the second circulator (1124), and is used to couple the reflected light of the sample arm light beam and the reference arm light beam, and is also used to emit the coupled light beam to the scanning acquisition imaging unit (113).

7. A method for using a multifunctional ophthalmic femtosecond device, characterized in that: The method comprises: Controlling the optical path switching unit (12) and the electrically controlled optical path switching mirror (23) to switch the multifunctional ophthalmic femtosecond device according to any one of claims 1 to 6 to the first OCT imaging, and turning on the first visible light camera (28); By observing the first visible light camera (28), the first objective lens (26) and the target tissue are controlled to move relative to each other, so that the negative pressure ring (27) is fixed on the target tissue, and the first cutting area is determined; Realignment is completed based on the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit (11) and the imaging in the first visible light camera (28).

8. The method according to claim 7, characterized in that The re-alignment is completed based on the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit (11) and the imaging in the first visible light camera (28), including: Determine the first center coordinates of the first cutting area in the XOZ section and the second center coordinates of the first cutting area in the YOZ section according to the two-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit (11); Determining the point coordinates of the first cutting area in the XOY plane according to the first center coordinates and the second center coordinates, and displaying them on the first visible light camera (28); The point coordinates are controlled to coincide with the indicating light spot to complete the realignment.

9. The method according to claim 7, characterized in that: The re-alignment is completed based on the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit (11) and the imaging in the first visible light camera (28), including: Performing three-dimensional reconstruction of the target tissue according to the three-dimensional OCT imaging displayed by the optical fiber light-emitting imaging unit (11) to generate a three-dimensional reconstructed image; Determining the coordinates of the interruption point of the first laser scan according to the three-dimensional reconstructed image, and displaying them in the first visible light camera (28); The coordinates of the interruption point are used as the starting point of re-treatment.

10. The method according to claim 7, characterized in that The method further comprises: Controlling the optical path switching unit (12) and the electrically controlled optical path switching mirror (23) to switch the multifunctional ophthalmic femtosecond device according to any one of claims 1 to 6 to the second OCT imaging, and turning on the second visible light camera (36); Determining the target tissue after cutting by observing a second visible light camera (36); Determining the incision opening of the target tissue through an eyepiece (31); The layer state of the separation hook when entering the target tissue is determined according to the two-dimensional OCT imaging or three-dimensional OCT imaging displayed by the optical fiber light output imaging unit (11).

Images