Ultrafast laser scanning system suitable for ophthalmologic operation

Abstract

The invention belongs to the related technical field of laser control, and discloses an ultrafast laser scanning system suitable for ophthalmologic surgery, which comprises a laser source, a light path adjusting structure and an eyeball fixing structure, and is characterized in that the light path adjusting structure comprises a scanner; the scanner comprises a first optical wedge prism, a second optical wedge prism, a third optical wedge prism and a fourth optical wedge prism which are sequentially arranged along a common axis, the direction of the common axis is the same as the direction of the central axis of incident light of the scanner, the first optical wedge prism and the second optical wedge prism are used for adjusting the scanning diameter, and the third optical wedge prism and the fourth optical wedge prism are used for adjusting scanning track patterns. Two groups of optical wedge prisms are combined, and each optical wedge prism is adjusted, so that laser scanning can be quickly carried out, the diameter of a scanning track and a scanning pattern can be flexibly adjusted, and the safety of an operation is improved.

Description

Technical Field

[0001] The present invention belongs to the technical field related to laser control, and more specifically, relates to an ultrafast laser scanning system suitable for ophthalmic surgery. Background Art

[0002] With the advancement of laser medical technology, femtosecond-assisted ophthalmic surgeries such as cataract surgery are being chosen by more and more patients for their safety and precision. Compared with traditional phacoemulsification surgery, femtosecond-assisted ophthalmic surgery has better treatment effects. Clinical studies have shown that the incisions of femtosecond-assisted ophthalmic surgery are highly repeatable and predictable, independent of the doctor's technical level, and more stable.

[0003] Taking femtosecond-assisted cataract surgery as an example, the operation requires the sequential execution of lens fission, capsule ring cutting and corneal lateral cutting. The cutting requirements at different stages are different. For example, the cutting area diameter of the lens fission is generally 4.0mm to 6.0mm, while the diameter of the corneal lateral cutting is generally 12mm. Most of the scanning devices currently used on the market are galvanometers, such as the Chinese patent CN 102573717B involved in Alcon ophthalmic equipment, which can achieve a series of operations such as lens fission, capsule ring cutting and corneal lateral cutting by controlling the galvanometer, but the scanning speed of the galvanometer is slow, which makes the laser cutting time longer. Generally speaking, the higher the degree of lens fragmentation, the more conducive to the operation, but the higher the degree of lens fragmentation, the more complex the required cutting trajectory, the longer the time required, and the higher the risk of negative pressure desorption of the eyeball.

[0004] The scanning speed of the dual wedge prism rotation scanning is relatively fast. For example, a dual wedge prism rotation scanning solution is proposed in Chinese patent CN 117331214 A. The scanning can be quickly realized by rotating the prism, and the rotation speed ratio of the two wedge prisms can be adjusted to obtain a petal-shaped scanning track with different densities. However, this solution cannot flexibly adjust the diameter of the petal-shaped scanning track. The scanning diameter depends on the wedge angle of the wedge prism used. Once the wedge prism is selected, the diameter of the scanning track is determined. For example, in order to adapt to the split nucleus of the lens, a wedge prism that satisfies the scanning track diameter of 5.0 mm is selected, but it cannot meet the 12 mm diameter requirement of the corneal side cut.

[0005] Therefore, how to flexibly adjust the scanning diameter and increase the laser scanning speed to quickly complete the entire laser cutting process is a technical problem that needs to be solved urgently. Summary of the invention

[0006] In view of the above defects or improvement needs of the prior art, the present invention provides an ultrafast laser scanning system suitable for ophthalmic surgery, which aims to flexibly adjust the scanning diameter and increase the laser scanning speed, quickly complete the entire laser cutting process, and thus reduce surgical risks.

[0007] To achieve the above-mentioned purpose, the present invention provides an ultrafast laser scanning system suitable for ophthalmic surgery, the ultrafast laser scanning system comprising a laser source, an optical path adjustment structure and an eyeball fixing structure, the laser source is used to emit laser light, the eyeball fixing structure is used to fix the patient's eyeball, the laser light is adjusted by the optical path adjustment structure and then scanned at a designated position of the patient's eyeball to achieve cutting, wherein the optical path adjustment structure comprises a scanner

[0008] The scanner includes: first to fourth wedge prisms arranged in sequence along a common axis, the direction of the common axis is the same as the direction of the central axis of the incident light of the scanner, the first wedge prism and the second wedge prism are used to adjust the diameter of the scanning track, the diameter of the scanning track is the diameter of the smallest circle covering the scanning track, and the third wedge prism and the fourth wedge prism are used to adjust the pattern shape of the scanning track.

[0009] Preferably, the optical path adjustment structure further includes a beam expander Z focuser and a focusing objective lens, wherein the beam expander Z focuser is used to adjust the focusing distance of the laser in the Z direction; and the focusing objective lens is used to converge the light to the patient's eyeball;

[0010] The laser emitted by the laser source is first adjusted for focusing distance by the beam expander Z focuser, and then the scanning trajectory is adjusted by the scanner, and the focusing objective lens focuses the light onto the patient's eyeball for laser cutting.

[0011] Preferably, the beam expander Z focuser comprises:

[0012] A first concave lens, used to diverge the parallel laser light emitted by the laser source;

[0013] The second convex lens is used to converge the divergent light emitted by the first concave lens.

[0014] Preferably, the optical path adjustment structure further includes:

[0015] A first beam splitter, used to reflect the output light of the scanner to the focusing objective lens, and transmit imaging light, wherein the imaging light includes anterior segment imaging light and intraoperative observation visible light;

[0016] A second beam splitter, used for reflecting the anterior segment imaging light and transmitting the intraoperative observation visible light;

[0017] The ultrafast laser scanning system also includes:

[0018] An anterior segment imaging module, used for receiving the anterior segment imaging light to realize anterior segment imaging of the patient;

[0019] The intraoperative imaging module is used to receive the intraoperative observation visible light to observe the scanning trajectory.

[0020] Preferably, the optical path adjustment structure further includes a controller, and the controller is used to control the scanner to enter the split nucleus mode, the capsule ring cutting mode and the corneal side cutting mode in sequence:

[0021] When entering the core splitting mode, firstly, adjusting the angle between the first optical wedge prism and the second optical wedge prism according to the diameter of the scanning track required for the core splitting and fixing the angle, then controlling the first to fourth optical wedge prisms to rotate in the same direction along the common axis and the first to third optical wedge prisms to rotate at the same speed, and adjusting the rotation speeds of the third optical wedge prism and the fourth optical wedge prism according to the pattern shape of the scanning track required for the core splitting to achieve the core splitting;

[0022] When entering the capsule ring cutting mode, firstly, the angle between the third optical wedge prism and the fourth optical wedge prism is adjusted to 0° and fixed, and the angle between the first optical wedge prism and the second optical wedge prism is adjusted and fixed according to the diameter of the scanning track required for the capsule ring cutting, and then the first to fourth optical wedge prisms are controlled to rotate in the same direction and at the same speed along the common axis to achieve capsule ring cutting;

[0023] When entering the corneal episiotomy mode, first adjust the angle between the first wedge prism and the second wedge prism according to the diameter of the scanning trajectory required for the corneal episiotomy and fix the angle, keep the angle between the third wedge prism and the fourth wedge prism at 0°, and then control the first to fourth wedge prisms to rotate in the same direction and at the same speed along the common axis to achieve corneal episiotomy.

[0024] Preferably, in the core splitting mode, the diameter range of the scanning track required for the core splitting is 4.0 mm to 6.0 mm.

[0025] Preferably, in the split-core mode, the rotation speed ratio of the third optical wedge prism and the fourth optical wedge prism ranges from 3 to 6.

[0026] Preferably, in the capsular ring cutting mode, the diameter of the scanning track required for the capsular ring cutting is 4.0 mm to 6.0 mm.

[0027] Preferably, in the corneal episiotomy mode, the diameter of the scanning track required for the corneal episiotomy is 11.0 mm to 13.0 mm.

[0028] Preferably, in the corneal episiotomy mode, only two incisions are made for the corneal episiotomy, the centers of the two incisions are located on the same diameter of the scanning trajectory, the length of one incision is 1.0 mm, and the length of the other incision is 2.0 mm.

[0029] Preferably, the initial angle of each wedge prism in the scanner is 0°, and when the angle of the first wedge prism and the second wedge prism is adjusted according to the diameter of the required scanning track in each mode, the first wedge prism is rotated half of the angle in the forward direction relative to the initial position, and the second wedge prism is rotated half of the angle in the reverse direction relative to the initial position.

[0030] In general, compared with the prior art, the above technical solutions conceived by the present invention mainly have the following beneficial effects:

[0031] The ultrafast laser scanning system suitable for ophthalmic surgery proposed in the present invention adopts two groups of wedge prisms in the scanner, the first wedge prism and the second wedge prism are the first group of wedge prisms, and the third wedge prism and the fourth wedge prism are the second group of wedge prisms. The diameter of the scanning track can be adjusted by adjusting the first wedge prism and the second wedge prism, and the pattern shape of the scanning track can be adjusted by adjusting the third wedge prism and the fourth wedge prism. By combining the two groups of wedge prisms and adjusting the rotation and relative position relationship of each wedge prism, the laser scanning can be performed quickly, and the diameter of the scanning track and the scanning pattern can be flexibly adjusted, thereby improving the safety of the operation.

[0032] Furthermore, a controller is also involved. The controller can perform specific control on the scanner. By adjusting the angle between the first optical wedge prism and the second optical wedge prism, the scanning diameter can be flexibly controlled. By adjusting the rotation speed ratio of the third optical wedge prism and the fourth optical wedge prism, the pattern of the scanning trajectory can be flexibly controlled. Based on the control scheme of the controller, laser operations in the nuclear splitting mode, capsule ring cutting mode and corneal epikeratography mode can be completed continuously without replacing the optical wedge prism in the middle, thereby improving the safety of the operation. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] Figure 1 is a schematic structural diagram of an ultrafast laser scanning system suitable for ophthalmic surgery in one embodiment of the present invention;

[0034] Figure 2 is a schematic diagram of an optical path when the included angle between the first wedge prism and the second wedge prism is 0 in one embodiment of the present invention;

[0035] Figure 3 1 is a schematic diagram of an optical path when the included angle between the first wedge prism and the second wedge prism is 180° in one embodiment of the present invention;

[0036] Figure 4 is a three-ring split-core trajectory formed when the rotation speed ratio of the third wedge prism and the fourth wedge prism in one embodiment of the present invention is 4;

[0037] Figure 5is a five-ring split-core trajectory formed when the rotation speed ratio of the third wedge prism and the fourth wedge prism in one embodiment of the present invention is 6;

[0038] Figure 6 is a schematic diagram of the trajectory of the capsule circumcision in one embodiment of the present invention;

[0039] Figure 7 is a schematic diagram of the trajectory of corneal lateral incision in one embodiment of the present invention;

[0040] Figure 8 is a schematic structural diagram of a beam expander Z focuser for controlling light beam collimation output in one embodiment of the present invention;

[0041] Fig. 9 is a structural schematic diagram of a beam expander Z focuser for controlling light beam divergence output in one embodiment of the present invention;

[0042] Fig.10 Detailed structural diagram of an ultrafast laser scanning system in one embodiment of the present invention. DETAILED DESCRIPTION

[0043] In order to make the purpose, technical solutions and advantages of the present invention more clearly understood, the present invention is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present invention and are not intended to limit the present invention. In addition, the technical features involved in the various embodiments of the present invention described below can be combined with each other as long as they do not conflict with each other.

[0044] like Figure 1 The figure shows a schematic diagram of the structure of an ultrafast laser scanning system suitable for ophthalmic surgery in one embodiment of the present invention. The ultrafast laser scanning system generally comprises a laser source, an optical path adjustment structure and an eyeball fixing structure. The laser source emits laser light, and the eyeball fixing structure is used to fix the patient's eyeball. The laser light is adjusted by the optical path adjustment structure and then scans the designated position of the patient's eyeball to achieve laser cutting. The optical path adjustment structure includes a scanner.

[0045] Specifically, the scanner includes a first wedge prism 31, a second wedge prism 32, a third wedge prism 33 and a fourth wedge prism 34 which are arranged in sequence along a common axis, and the direction of the common axis is the same as the central axis direction of the incident light of the scanner.

[0046] In the present invention, two groups of wedge prisms are provided, the first wedge prism 31 and the second wedge prism 32 are the first group of wedge prisms, which are mainly used to adjust the scanning diameter, the third wedge prism 33 and the fourth wedge prism 34 are the second group of wedge prisms, which are mainly used to adjust the pattern of the scanning trajectory, and by combining the two groups of wedge prisms and adjusting the rotation of each wedge prism, the laser scanning can be performed quickly and the diameter of the scanning trajectory and the scanning pattern can be flexibly adjusted.

[0047] Furthermore, the invention also comprises a controller, which is used to control the scanner to enter the nuclear splitting mode, the capsule ring cutting mode and the corneal side cutting mode in sequence.

[0048] At the initial moment, the initial included angle of each wedge prism can be set to 0°.

[0049] When entering the split-core mode, first adjust the angle between the first optical wedge prism 31 and the second optical wedge prism 32 according to the diameter of the split-core scanning trajectory and fix the angle, then control the first optical wedge prism 31, the second optical wedge prism 32, the third optical wedge prism 33 and the fourth optical wedge prism 34 to rotate in the same direction along a common axis and the rotation speeds of the first optical wedge prism 31, the second optical wedge prism 32 and the third optical wedge prism 33 are the same, and adjust the rotation speeds of the third optical wedge prism 33 and the fourth optical wedge prism 34 according to the pattern of the split-core scanning trajectory to achieve the split-core.

[0050] Specifically, the included angles of the first wedge prism 31 and the second wedge prism 32 are different, and the diameters of the scanning tracks are different. Therefore, after determining the diameter of the scanning track, the included angle of the first wedge prism 31 and the second wedge prism 32 can be directly calculated according to the optical path. Generally, in the split-core mode, the diameter of the split-core scanning track ranges from 4.0 mm to 6.0 mm. The diameter of the split-core scanning track is the diameter of the smallest circle covering the split-core scanning track.

[0051] like Figure 2 FIG. 1 is a schematic diagram of an optical path when the angle between the first wedge prism and the second wedge prism is 0° in one embodiment of the present invention, the optical path deflection is θ2, and the scanning distance is r2. Figure 3 FIG. 1 is a schematic diagram of an optical path when the included angle between the first wedge prism and the second wedge prism is 180° in one embodiment of the present invention, the optical path deflection is θ1, and the scanning distance is r1.

[0052] Specifically, after the diameter of the scanning track is determined, the angle between the first wedge prism 31 and the second wedge prism 32 can be directly calculated according to the optical path. The relationship between the angle and the diameter is given below:

[0053] D=2·L·tan(-kγ 2 )

[0054] Wherein, D is the scanning diameter; L is the distance between the four-wedge prism and the imaging surface; γ is the wedge angle; k is the proportional coefficient, which is obtained through experimental calibration measurement after the scanning system is fixed.

[0055] Specifically, if the rotation speed ratio of the third wedge prism 33 and the fourth wedge prism 34 is different, the pattern of the scanning trajectory of the split core will be different. The split core mode is to achieve the splitting of the lens core. The higher the degree of lens fragmentation, the more complex the required cutting trajectory and the longer the time required. Therefore, the pattern of the scanning trajectory of the split core can be preset according to the needs in advance, and then the rotation speed ratio of the third wedge prism 33 and the fourth wedge prism 34 can be determined according to the preset pattern. Specifically, the rotation speed ratio range is 3 to 6, which can meet the requirements of split core fragmentation. The larger the rotation speed ratio, the more petals of the scanning pattern and the more complex the trajectory. Figure 4 FIG. 4 shows a three-ring split-core trajectory formed when the rotation speed ratio of the third wedge prism and the fourth wedge prism is 4 in one embodiment of the present invention, which forms a three-ring split-core trajectory 39 on the lens 35. Figure 5 The figure shows a five-ring split-core trajectory formed when the rotation speed ratio of the third wedge prism and the fourth wedge prism is 6 in one embodiment of the present invention, which forms a five-ring split-core trajectory 40 on the lens 35.

[0056] After determining the angle between the first wedge prism and the second wedge prism and the rotation speed ratio between the third wedge prism and the fourth wedge prism, the wedge prism is rotated according to the determined parameters. In the core splitting mode, the first wedge prism 31, the second wedge prism 32, the third wedge prism 33 and the fourth wedge prism 34 rotate in the same direction along a common axis and the first wedge prism 31, the second wedge prism 32 and the third wedge prism 33 have the same rotation speed. The third wedge prism 33 and the fourth wedge prism 34 rotate according to the calculated rotation speed ratio, so that the cutting of a preset pattern can be achieved in a preset area. The femtosecond laser performs complex trajectory cutting in the turbid lens to split the lens and complete the lens core splitting operation.

[0057] After completing the lens nucleus splitting operation, enter the capsule cutting mode.

[0058] When entering the capsule ring cutting mode, first adjust the angle between the third optical wedge prism 33 and the fourth optical wedge prism 34 to 0° and fix the angle, adjust the angle between the first optical wedge prism 31 and the second optical wedge prism 32 according to the diameter of the capsule ring cutting scanning trajectory and fix the angle, and then control the first optical wedge prism 31, the second optical wedge prism 32, the third optical wedge prism 33 and the fourth optical wedge prism 34 to rotate in the same direction and speed along the common axis to achieve capsule ring cutting.

[0059] Specifically, the scanning trajectory of capsular annulus resection is a circle. At this time, the angle between the third optical wedge prism 33 and the fourth optical wedge prism 34 is adjusted to 0°, and they rotate in the same direction and at the same speed, so that the scanning trajectory is a circle. In addition, the angle between the first optical wedge prism 31 and the second optical wedge prism 32 is adjusted according to the diameter of the capsular annulus resection scanning trajectory. If the diameter of the capsular annulus resection scanning trajectory is the same as the diameter of the split-core scanning trajectory, the angle between the first optical wedge prism 31 and the second optical wedge prism 32 in the split-core mode can be directly maintained. After adjusting the angle, the first optical wedge prism 31, the second optical wedge prism 32, the third optical wedge prism 33 and the fourth optical wedge prism 34 are controlled to rotate in the same direction and at the same speed along the common axis to achieve capsular annulus resection. In a specific embodiment, the diameter of the capsular annulus resection scanning trajectory is 4.0 mm to 6.0 mm, generally 5.0 mm. Figure 6 FIG. 1 is a schematic diagram of a capsule cutting trajectory in an embodiment of the present invention, which forms a circular capsule cutting trajectory 36 on the lens 35 .

[0060] After completing the capsule cutting operation, enter the corneal side cutting mode.

[0061] When entering the corneal episiotomy mode, first adjust the angle between the first optical wedge prism 31 and the second optical wedge prism 32 according to the diameter of the corneal episiotomy scanning trajectory and fix the angle, keep the angle between the third optical wedge prism 33 and the fourth optical wedge prism 34 at 0°, and then control the first optical wedge prism 31, the second optical wedge prism 32, the third optical wedge prism 33 and the fourth optical wedge prism 34 to rotate in the same direction and at the same speed along the common axis to achieve corneal episiotomy.

[0062] Specifically, the scanning trajectory of corneal episiotomy is a circle, and the diameter of the scanning trajectory is the largest, generally 11.0mm to 13.0mm, for example, 12mm. Therefore, it is also necessary to first adjust the angle between the first wedge prism 31 and the second wedge prism 32 according to the diameter of the corneal episiotomy scanning trajectory and fix the angle. Since the angle between the third wedge prism 33 and the fourth wedge prism 34 is 0° during capsule ring cutting, during corneal episiotomy, it is sufficient to continue to maintain the angle between the third wedge prism 33 and the fourth wedge prism 34 at 0°. Then control the first wedge prism 31, the second wedge prism 32, the third wedge prism 33 and the fourth wedge prism 34 to rotate in the same direction and at the same speed along the common axis to achieve corneal episiotomy. Corneal episiotomy only requires cutting a number of intermittent small incisions. Therefore, during laser scanning, the positions that do not need to be cut can be shielded during light blocking to expose the positions that need to be cut. Figure 7 The figure shows a schematic diagram of the trajectory of corneal side cutting in one embodiment of the present invention, which forms a corneal side cutting scanning trajectory on the cornea 38, and actually forms two incisions, one with a length of 1.0 mm and the other with a length of 2.0 mm.

[0063] In specific operation, before the scanner scans, each wedge prism is in an initial position and the initial angle of each wedge prism is 0°. When entering the scanning period, when adjusting the angle of the first wedge prism and the second wedge prism according to the diameter of the scanning track in each mode, the first wedge prism is rotated half of the angle in the positive direction relative to the initial position, and the second wedge prism is rotated half of the angle in the negative direction relative to the initial position. Taking the adjustment angle of the first and second prisms as 30° as an example, the first and second prisms need to be rotated 15° respectively, that is, the first prism is rotated 15° forward and the second prism is rotated 15° reversely, and the relative rotation angle is 30°. After adjusting the angle, the laser is turned on and the four wedge prisms are controlled to rotate. In this way, the initial position of the scanning track in each mode can be accurately obtained, which is conducive to matching the laser light emission timing with the scanning speed and realizing the equidistant blasting of laser pulses.

[0064] In one embodiment, the optical path adjustment structure also includes a beam expander Z focuser and a focusing objective lens. The beam expander Z focuser is used to adjust the focusing distance of the laser in the Z direction; the focusing objective lens is used to converge the light onto the patient's eyeball; the laser emitted by the laser source is first adjusted for focusing distance by the beam expander Z focuser, and then the scanning trajectory is adjusted by the scanner and the focusing objective lens focuses the light onto the patient's eyeball for laser cutting.

[0065] In one embodiment, the beam expander Z focuser includes a first concave lens and a second convex lens, wherein the first concave lens is used to diverge the parallel laser light emitted by the laser source, and the second convex lens is used to converge the divergent light emitted by the first concave lens.

[0066] like Figure 8 This is a schematic diagram of the structure of a beam expander Z focuser for controlling the collimated output of a light beam in one embodiment of the present invention. The focal length of the first concave lens is -f1, and the focal length of the second convex lens is f2. When the distance between the two lenses is L=f2-f1, the output light beam is collimated, and the laser is focused on the focal plane.

[0067] like Fig. 9 The schematic diagram of the structure of the beam expander Z focuser for controlling the divergent output of the light beam in one embodiment of the present invention is as follows. When the distance between the two lenses L>f2-f1, the output light beam diverges and the laser is focused below the focal plane. By adjusting the L value, the axial spot focus position can be adjusted, thereby achieving axial focusing.

[0068] Specifically, the optical path adjustment structure also includes a first beam splitter and a second beam splitter: the first beam splitter is used to reflect the output light of the scanner to the focusing objective lens, and transmit the imaging light, the imaging light includes the anterior segment imaging light and the visible light for intraoperative observation; the second beam splitter is used to reflect the anterior segment imaging light and transmit the visible light for intraoperative observation; the ultrafast laser scanning system also includes an anterior segment imaging module and an intraoperative imaging module, the anterior segment imaging module is used to receive the anterior segment imaging light to realize the anterior segment imaging of the patient; the intraoperative imaging module is used to receive the visible light for intraoperative observation to observe the scanning trajectory.

[0069] like Fig.10 The figure shows a detailed structural diagram of an ultrafast laser scanning system in an embodiment of the present invention, wherein a laser source 1 is used to provide a light source for laser processing, and a high-power laser source may be a high-power continuous laser or a high-power ultrashort pulse laser, and the laser wavelength covers ultraviolet wavelengths, visible light wavelengths, and infrared wavelengths; a beam expander Z focuser 2 is used for axial scanning of the light beam; a prism scanner 3 is used for XY two-dimensional scanning; a focusing objective lens 4 is used to converge the light beam; anterior segment imaging 5 is used for anterior segment imaging of the patient; intraoperative imaging 6 is used for intraoperative observation of the scanning trajectory; a negative pressure interface 7 is used to fix the patient's eyeball; a beam splitter 9 is used to reflect processing light and transmit imaging light; a beam splitter 10 is used to reflect anterior segment imaging light and transmit visible light for intraoperative observation.

[0070] The ultrafast laser scanning system suitable for ophthalmic surgery proposed by the present invention adopts two groups of wedge prisms in the scanner. The first wedge prism and the second wedge prism form the first group of wedge prisms. By adjusting the angle between the first wedge prism and the second wedge prism, the scanning diameter can be flexibly adjusted. The third wedge prism and the fourth wedge prism form the second group of wedge prisms. By adjusting the rotation speed ratio of the third wedge prism and the fourth wedge prism, the pattern of the scanning trajectory can be flexibly adjusted. By combining the two groups of wedge prisms and adjusting the rotation and relative position relationship of each wedge prism, laser scanning can be performed quickly, and the diameter of the scanning trajectory and the scanning pattern can be flexibly adjusted, thereby improving the safety of the operation.

[0071] The technical features of the above embodiments can be combined arbitrarily. To make the description concise, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification. It should be noted that "in one embodiment", "for example", "for example", etc. of the present invention are intended to illustrate the present invention, rather than to limit the present invention.

[0072] The above embodiments only express several implementation methods of the present invention, and the descriptions thereof are relatively specific and detailed, but they cannot be understood as limiting the scope of the patent application. It should be pointed out that, for ordinary technicians in this field, several variations and improvements can be made without departing from the concept of the present invention, and these all belong to the protection scope of the present invention.

Claims

1. An ultrafast laser scanning system suitable for ophthalmic surgery, characterized in that: It comprises a laser source, an optical path adjustment structure and an eyeball fixing structure, wherein the laser source is used to emit laser light, the eyeball fixing structure is used to fix the patient's eyeball, and the laser light is adjusted by the optical path adjustment structure to perform laser scanning at a designated position of the patient's eyeball to achieve cutting, wherein the optical path adjustment structure comprises a scanner; The scanner includes: first to fourth wedge prisms arranged in sequence along a common axis, the direction of the common axis is the same as the direction of the central axis of the incident light of the scanner, the first wedge prism and the second wedge prism are used to adjust the diameter of the scanning track, the diameter of the scanning track is the diameter of the smallest circle covering the scanning track, and the third wedge prism and the fourth wedge prism are used to adjust the pattern shape of the scanning track.

2. The ultrafast laser scanning system according to claim 1, characterized in that: The optical path adjustment structure also includes a beam expander Z focuser and a focusing lens: the beam expander Z focuser is used to adjust the focusing distance of the laser; the focusing lens is used to converge the light to the patient's eyeball; The laser emitted by the laser source is first adjusted for focusing distance by the beam expander Z focuser, and then the diameter and pattern shape of the scanning track are adjusted by the scanner, and the focusing objective lens focuses the light onto the patient's eyeball for laser cutting.

3. The ultrafast laser scanning system according to claim 2, characterized in that: The beam expander Z focuser comprises: A first concave lens, used to diverge the parallel laser light emitted by the laser source; The second convex lens is used to converge the divergent light emitted by the first concave lens.

4. The ultrafast laser scanning system according to claim 2, characterized in that: The optical path adjustment structure also includes: A first beam splitter, used to reflect the output light of the scanner to the focusing objective lens, and transmit imaging light, wherein the imaging light includes anterior segment imaging light and intraoperative observation visible light; A second beam splitter, used for reflecting the anterior segment imaging light and transmitting the intraoperative observation visible light; The ultrafast laser scanning system also includes: An anterior segment imaging module, used for receiving the anterior segment imaging light to realize anterior segment imaging of the patient; The intraoperative imaging module is used to receive the intraoperative observation visible light to observe the scanning trajectory.

5. The ultrafast laser scanning system according to any one of claims 1 to 4, characterized in that: The optical path adjustment structure also includes a controller, which is used to control the scanner to enter the split nucleus mode, the capsule ring cutting mode and the corneal side cutting mode in sequence: When entering the core splitting mode, firstly, adjusting the angle between the first optical wedge prism and the second optical wedge prism according to the diameter of the scanning track required for the core splitting and fixing the angle, then controlling the first to fourth optical wedge prisms to rotate in the same direction along the common axis and the first to third optical wedge prisms to rotate at the same speed, and adjusting the rotation speeds of the third optical wedge prism and the fourth optical wedge prism according to the pattern shape of the scanning track required for the core splitting to achieve the core splitting; When entering the capsule ring cutting mode, firstly, the angle between the third optical wedge prism and the fourth optical wedge prism is adjusted to 0° and fixed, and the angle between the first optical wedge prism and the second optical wedge prism is adjusted and fixed according to the diameter of the scanning track required for the capsule ring cutting, and then the first to fourth optical wedge prisms are controlled to rotate in the same direction and at the same speed along the common axis to achieve capsule ring cutting; When entering the corneal episiotomy mode, first adjust the angle between the first wedge prism and the second wedge prism according to the diameter of the scanning trajectory required for the corneal episiotomy and fix the angle, keep the angle between the third wedge prism and the fourth wedge prism at 0°, and then control the first to fourth wedge prisms to rotate in the same direction and at the same speed along the common axis to achieve corneal episiotomy.

6. The ultrafast laser scanning system according to claim 5, characterized in that: In the nucleus splitting mode, the diameter range of the scanning track required for the nucleus splitting is 4.0 mm to 6.0 mm. In the capsule ring cutting mode, the diameter of the scanning track required for the capsule ring cutting is 4.0 mm to 6.0 mm.

7. The ultrafast laser scanning system according to claim 5, characterized in that: In the split-core mode, the rotation speed ratio of the third wedge prism and the fourth wedge prism ranges from 3 to 6.

8. The ultrafast laser scanning system according to claim 5, characterized in that: In the corneal episiotomy mode, the diameter of the scanning track required for the corneal episiotomy is 11.0 mm to 13.0 mm.

9. The ultrafast laser scanning system according to claim 5, characterized in that: In the corneal episiotomy mode, only two incisions are made in the corneal episiotomy, the centers of the two incisions are located on the same diameter of the scanning track, the length of one incision is 1.0 mm, and the length of the other incision is 2.0 mm.

10. The ultrafast laser scanning system according to claim 5, characterized in that: The initial angle of each wedge prism in the scanner is 0°. When the angle between the first wedge prism and the second wedge prism is adjusted according to the diameter of the required scanning track in each mode, the first wedge prism is rotated half of the angle in the forward direction relative to the initial position, and the second wedge prism is rotated half of the angle in the reverse direction relative to the initial position.

Images