CN219307130U - Ophthalmic laser objective scanning device and laser system - Google Patents

Abstract

The utility model relates to the technical field of medical equipment, and provides an ophthalmic laser object lens scanning device and a laser system, wherein the ophthalmic laser object lens scanning device comprises: the rotary table and the linear motion assembly; the rotary table is rotatably arranged around a first axis, and the first axis passes through the rotary table; the linear motion assembly is arranged on the rotary table and rotates along with the rotary table, and is used for installing the objective lens and driving the objective lens to linearly move along a second axis so as to change the distance between the objective lens and the first axis, and the second axis is intersected with the first axis. The objective lens scanning device is more beneficial to forming a spiral or concentric scanning track, has the characteristics of high-speed scanning and high precision, shortens the laser scanning time to the maximum extent, further improves the phenomenon that the negative pressure suction device damages the fundus or loses negative pressure, and ensures higher scanning quality.

Description

Ophthalmic laser objective scanning device and laser system

Technical Field

The utility model relates to the technical field of medical instruments, in particular to an ophthalmic laser object lens scanning device and a laser system.

Background

With the development of laser technology, laser surgery is becoming the first means of optical correction for ophthalmology. Based on different requirements, different laser eye surgery systems can be selected to provide different types of laser beams, such as ultraviolet laser, infrared laser and near infrared ultrashort pulse laser.

Femtosecond laser is an ultra-short pulse width, high repetition frequency, low single pulse energy, infrared pulse laser capable of precisely cutting a stromal layer without damaging a corneal epithelium and a pre-elastic layer and with little heat transfer, and thermal damage of a cutting area, so that the femtosecond laser has been widely used for eye surgery including refractive treatment, cornea transplantation, cataract treatment, glaucoma treatment, etc., among which the most widely used ones.

The current primary application of refractive therapy in China is myopia correction. The mainstream technology of myopia correction surgery comprises excimer laser source cornea milling and microlens manufacturing and extraction. The principle of LASIK operation is that a corneal flap is firstly made on the upper portion of cornea stroma, then the cornea stroma is individually cut by using excimer laser so as to attain the goal of correcting vision. The method for manufacturing the cornea flap can use a tool to manually manufacture the flap, and can also use a femtosecond laser to manufacture the flap. Wherein the thickness of the corneal flap made using a femtosecond laser is accurate and iatrogenic infections introduced by the use of lamellar knives can be avoided.

The micro lens manufacturing and extraction operation is to manufacture a micro lens in cornea stroma by using a femtosecond laser, manufacture a micro incision by using the femtosecond laser, and finally extract the micro lens through the micro incision. This mode of lens fabrication and extraction surgery is known as full femtosecond laser surgery. Full femtosecond laser surgery is currently mainly referred to as SMILE surgery, i.e., femtosecond laser small incision corneal microlens extraction.

The main principle is that a laser and a scanning system are controlled to focus on cornea tissues according to a preset pulse laser sequence, and then light damage is generated through the interaction of laser pulses and the cornea tissues, so that a plurality of cavitation bubbles are generated, and a cornea cutting surface is separated from a cornea, so that the cornea flap or the micro lens is manufactured. The flap only needs to cut off one surface of the separation flap that is connected to the corneal tissue, and the tiny lens needs to be extracted, so that both the front surface and the back surface that are connected to the corneal tissue need to be separated.

Femto second laser surgery still needs to be in the same place eyeball and laser equipment fixed through negative pressure suction device, and if negative pressure time is too long, probably brings the damage to the eyeground, also can increase the probability that negative pressure was lost. Therefore, the scanning time of the femtosecond laser operation should be shortened as much as possible, so as to reduce the probability of fundus damage and the probability of negative pressure loss.

Currently, in the femto-second device on the market, an XYZ scanner is used to drive an objective lens to move, and the objective lens is driven to move along the X direction, the Y direction and the Z direction to realize raster scanning. Since the human eye is ellipsoidal, the cross section to be separated is circular or curved, and thus the interface to be scanned is also curved. The scanning track of the XYZ scanner needs to adapt to the curved shape of the eyeball. On the one hand, the scanning speed is slower, so that the whole scanning time is longer, the probability of damaging fundus oculi or losing negative pressure of the negative pressure suction device is larger, the X-direction and Y-direction are needed to realize high-speed scanning if the scanning speed is to be improved, the X-direction scanner and the Y-direction scanner are usually realized by utilizing two linear motors or two vibrating mirrors to be matched with each other at present, but the high-speed linear motors and the two-dimensional vibrating mirrors which hardly meet the application at present are adopted, and the cost of the scanner is obviously increased even if the high-speed scanning is realized by the means. On the other hand, this scanner is liable to form a zigzag scanning track on the fundus, and the scanning quality is poor.

Therefore, there is a need for an ophthalmic laser objective scanning device and a laser system, which improve the driving manner of the existing objective in the linear motion along the X-direction and the Y-direction, so as to satisfy the high scanning speed and ensure the higher scanning quality.

Disclosure of Invention

The utility model provides an ophthalmic laser object lens scanning device and a laser system, wherein the scanning device is favorable for realizing spiral or concentric circular scanning tracks through the cooperation of rotary scanning motion and linear scanning motion, can be better adapted to curved surface-shaped scanning scenes of eyeballs, has the characteristics of high-speed scanning and high precision, can efficiently and quickly realize tissue cutting separation in tissues such as cornea, crystalline lens and the like, shortens the laser scanning time to the maximum extent, further improves the phenomenon that a negative pressure suction device damages fundus or loses negative pressure, and meanwhile, the scanning device utilizes the characteristic of high-speed rotation, has smoother scanning circumferential tracks, ensures higher scanning quality, can be applied to various eye tissue separation operations such as cornea, crystalline lens capsule, crystalline lens and glass body and the like, and has multifunction and wider adaptation.

The ophthalmic laser objective scanning device comprises: the rotary table and the linear motion assembly;

the rotary table is rotatably arranged around a first axis, and the first axis passes through the rotary table;

the linear motion assembly is arranged on the rotary table and rotates along with the rotary table, and is used for installing an objective lens and driving the objective lens to linearly move along a second axis so as to change the distance between the objective lens and the first axis, and the second axis intersects with the first axis;

the linear motion assembly is configured to: when the objective lens is mounted on the linear motion assembly, the main optical axis of the objective lens is parallel to the first axis, and the projection of the objective lens and the turntable along the direction of the first axis is not coincident.

Optionally, the second axis is perpendicular to the first axis.

Optionally, the rotary table is provided with an installation cavity, the installation cavity penetrates through the rotary table along the direction of the first axis, and the linear motion assembly is arranged in the installation cavity.

Optionally, the rotary table has a cylindrical outer profile, the first axis being collinear with a central axis of the rotary table.

Optionally, the mounting cavity is a cylindrical cavity, and the first axis is collinear with a central axis of the mounting cavity.

Optionally, the linear motion assembly can move telescopically along the second axis, one end of the linear motion assembly along the first axis is connected to the inner wall of the mounting cavity, and the other end of the linear motion assembly is used for being connected with the objective lens.

The utility model also provides a laser system which comprises an objective lens and the ophthalmic laser object lens scanning device, wherein the objective lens is arranged on the linear motion assembly.

Optionally, the laser system further comprises a controller, a laser source and a light guide assembly;

the laser source is used for generating a laser beam;

the light guide assembly is used for guiding the laser beam to be transmitted to the objective lens along the direction parallel to the main optical axis of the objective lens, and the laser beam forms a focus after passing through the objective lens;

the object lens scanning device of the ophthalmic laser is used for driving the object lens to move;

the controller is used for matching the movement of the objective lens with the light guide assembly so that the focus forms a spiral scanning track or a concentric circle scanning track along with the movement of the objective lens.

Optionally, the laser system further comprises an energy controller disposed on the transmission path of the laser beam for changing the pulse energy of the laser beam.

Optionally, the laser system further comprises a light shutter, and the light shutter is arranged on a transmission path of the laser beam between the laser source and the light guide component and is used for controlling on-off of the transmission path of the laser beam.

In summary, the ophthalmic laser objective scanning device includes: the rotary table and the linear motion assembly; the rotary table is rotatably arranged around a first axis, and the first axis passes through the rotary table; the linear motion assembly is arranged on the rotary table and rotates along with the rotary table, and is used for installing an objective lens and driving the objective lens to linearly move along a second axis so as to change the distance between the objective lens and the first axis, and the second axis intersects with the first axis; the linear motion assembly is configured to: when the objective lens is mounted on the linear motion assembly, the main optical axis of the objective lens is parallel to the first axis, and the projection of the objective lens and the turntable along the direction of the first axis is not coincident.

So configured, the objective lens scanning device of the present utility model makes the motion track of the objective lens rotate around the first axis and move linearly along the second axis, which is more beneficial to forming a spiral or concentric scanning track, so that the scanning track of the laser beam is more suitable for the curved surface shape of the eyeball; a spiral or concentric circular scan trajectory is more suitable for a cut scan requiring a circular or curved cross-section to be separated than a conventional linear motion raster scan trajectory in the X-direction and in the Y-direction. The fast rotary motion of revolving stage is convenient for realize, cooperates objective along second axis rectilinear motion for this scanning device has high-speed scanning and high accuracy characteristic, can match laser pulse's high repetition frequency, can realize the tissue cutting separation in tissues such as cornea and crystalline lens high-efficient quick, furthest shortens laser scanning time, and then improves negative pressure suction device and damage fundus or negative pressure loss's phenomenon. Meanwhile, the scanning device utilizes the characteristic of high-speed rotation, the scanning circumferential track is smoother, the higher scanning quality is ensured, the scanning device can be applied to scenes with higher scanning quality requirements, for example, the scanning device can be applied to various eye tissue separation operations such as cornea, lens capsule, lens, vitreous body and the like, and the laser operation system has multifunction and wider application.

Drawings

FIG. 1 is a schematic diagram of a laser system according to an embodiment of the present utility model;

fig. 2 is a schematic structural diagram of an objective lens scanning device of an ophthalmic laser according to a first embodiment of the present utility model;

fig. 3 is a schematic structural diagram of an ophthalmic laser objective scanning device according to a second embodiment of the present utility model.

Wherein, the reference numerals are as follows:

a 10-ophthalmic laser objective scanning device; 11-a rotary table; 12-a linear motion assembly;

20-a driver;

30-an objective lens;

40-a laser source;

50-a light guide assembly;

60-a controller;

70-energy controller;

80-shutter;

91-laser beam; 92-corneal contact lens; 93-scanning the track; 94-eyeball;

a-a first axis; b-a second axis.

Detailed Description

The following describes the object lens scanning device of the ophthalmic laser according to the present utility model in further detail with reference to the accompanying drawings and the specific embodiments. The advantages and features of the present utility model will become more apparent from the following description. It should be noted that the drawings are in a very simplified form and are all to a non-precise scale, merely for convenience and clarity in aiding in the description of embodiments of the utility model.

In the present utility model, "proximal" and "distal" are relative orientations, relative positions, directions of elements or actions relative to each other from the perspective of a physician using the product, and "proximal" and "distal" generally refer to the end that first enters the patient, while "proximal" and "distal" generally refer to the opposite end of "distal" are not limiting.

In the utility model, the outer diameter and the inner diameter correspond to the diameter size for a circular structure, the inner diameter refers to the diameter of an inscribed circle of the circular structure for a non-circular structure, and the outer diameter refers to the diameter of an circumscribed circle of the circular structure; the axial direction corresponds to the direction in which the axis is located for cylindrical rods, and corresponds to the length direction of rods for non-cylindrical rods.

As used in this disclosure, the singular forms "a," "an," and "the" include plural referents, the term "or" are generally used in the sense of comprising "and/or" and the term "several" are generally used in the sense of comprising "at least one," the term "at least two" are generally used in the sense of comprising "two or more," and the term "first," "second," and "third" are used for descriptive purposes only and are not to be construed as indicating or implying any relative importance or number of features indicated. Thus, a feature defining "a first", "a second", "a third" may include one or at least two such features, either explicitly or implicitly. Furthermore, as used in this disclosure, "mounted," "connected," and "disposed" with respect to another element should be construed broadly to mean generally only that there is a connection, coupling, mating or transmitting relationship between the two elements, and that there may be a direct connection, coupling, mating or transmitting relationship between the two elements or indirectly through intervening elements, and that no spatial relationship between the two elements is to be understood or implied, i.e., that an element may be in any orientation, such as internal, external, above, below, or to one side, of the other element unless the context clearly dictates otherwise. The specific meaning of the above terms in the present utility model can be understood by those of ordinary skill in the art according to the specific circumstances. Furthermore, directional terms, such as above, below, upper, lower, upward, downward, left, right, etc., are used with respect to the exemplary embodiments as they are shown in the drawings, upward or upward toward the top of the corresponding drawing, downward or downward toward the bottom of the corresponding drawing.

Embodiment one:

the present embodiment provides a laser system comprising an ophthalmic laser objective scanning device 10, an objective lens 30, a laser source 40, a light guide assembly 50, a controller 60, an energy controller 70, and a shutter 80.

Referring to fig. 1, the energy controller 70 is located between the laser source 40 and the light guide assembly 50, and the shutter 80 is located between the energy controller 70 and the light guide assembly 50; the laser beam generated by the laser source 40 is sequentially transmitted to the objective lens 30 through the energy controller 70, the shutter 80, and the light guide assembly 50, and then focused to a target position through the objective lens 30.

The laser source 40 is configured to generate a pulsed laser beam comprising a plurality of laser pulses; the laser source 40 may employ a conventional laser, which may be a femtosecond laser capable of providing a pulsed laser beam that may be used for optical correction, such as localized photodisruption, which may be disposed at or below the surface of tissue or other material to form a high precision machining cut. For example, micro-optical scanning systems may be used to scan pulsed laser beams to create incisions or petals in the tissue, form removable structures for the tissue, and the like. In other embodiments, the laser may be configured to generate an ultraviolet laser beam comprising a plurality of ultraviolet laser pulses capable of photodecomposition of one or more intraocular targets within the eye.

The energy controller 70 is used to vary the pulse energy of the laser beam. The energy controller 70 may employ a known device, for example, an attenuator, which may be composed of a zero-order half-wave plate and a brewster-type thin film polarizer, the zero-order half-wave plate may rotate polarization, the brewster-type thin film polarizer may pass P-type polarization and reflect S-type polarized laser beams, the wave plate and the polarizer may be coated according to a desired wavelength, the energy control is implemented by electrically rotating the half-wave plate, the attenuator is an existing device, and a corresponding specification and model may be selected based on a use requirement.

The optical shutter 80 is used for controlling the on-off of the laser beam transmission path, the optical shutter 80 can be opened for the laser path to pass through, or closed for blocking the laser beam to pass through, so as to control whether the laser beam is transmitted to the lens, the optical shutter 80 is the existing equipment, and the corresponding specification and model can be selected based on the use requirement; and will not be described in detail herein.

The light guide assembly 50 is used for reflecting the laser beam emitted by the laser source 40, so that the laser beam is transmitted to the objective lens 30 through the beam expansion and reflection of the optical components, and the light guide assembly 50 is also used for adjusting the incidence position of the laser beam relative to the objective lens 30, and matching with the movement of the objective lens 30, so that the final laser beam moves along the expected scanning track through the focus of the objective lens 30. By the movement of the light guide assembly 50 and the cooperation of the objective lens 30, the movement of the focal point of the laser beam along the scanning track is finally achieved. The light guide assembly 50 is an existing device, and can realize laser beam movement through an XY scanner, a Z scanner and optical devices such as a resonance scanner in cooperation, so as to adjust the incident position of the objective lens 30, and the light guide assembly 50 can adopt an existing light guide arm, and can select a corresponding specification model based on the use requirement; and will not be described in detail herein.

The objective lens 30 is mainly used for focusing the passing laser beam at a target position, and the objective lens 30 is connected with the linear motion assembly 12, wherein the ophthalmic laser object lens scanning device 10 is used for driving the objective lens 30 to move, so that the objective lens 30 follows the laser beam to move, and further, the objective lens 30 moves to form a scanning track of a focus of the laser beam.

The optical laser objective scanning device 10 of the present utility model is mainly used for replacing the existing driving structure of the objective lens moving linearly along the X-direction and the Y-direction, i.e. in the actual use process, the optical laser objective scanning device 10 needs to be matched with the Z-direction driving structure for use to adjust the depth of the focus.

The ophthalmic laser objective scanning device 10 is used for controlling the movement of the objective lens 30, and in combination with the driving of the objective lens 30 by the Z-direction driving structure in the direction parallel to the first axis a, the controller in the laser system controls the laser pulses to be focused to the eyeball 94 through the contact lens 92 in the patient adapter according to a predetermined sequence, and cavitation bubbles are formed by the photodisruption principle of the laser pulses so as to separate the cornea tissues, so as to manufacture the corneal flap or the cornea microlens.

Referring to fig. 1 and 2, an ophthalmic laser objective scanning device 10 includes: a rotary table 11 and a linear motion assembly 12;

the rotary table 11 is rotatably provided around a first axis a passing through the rotary table 11; the linear motion assembly 12 is arranged on the rotary table 11 and rotates along with the rotary table 11, and the linear motion assembly 12 is used for installing an objective lens 30 and driving the objective lens 30 to linearly move along a second axis b relative to the rotary table 11, and the second axis b intersects with the first axis a; when the objective lens 30 is mounted on the linear motion assembly 12, the main optical axis of the objective lens 30 is parallel to the first axis a, and the projection of the objective lens 30 and the turntable 11 along the direction of the first axis a is not coincident, so that the turntable 11 does not block the incident and emergent laser beams of the objective lens 30. The second axis b is herein understood to be stationary with respect to the turntable 11, so that during rotation of the turntable 11 the second axis b is adapted to rotate with the turntable.

The objective lens scanning device of the present embodiment makes the motion track of the objective lens 30 be a rotation motion around the first axis a and a linear motion along the second axis b, which is more beneficial to forming a spiral scanning track 93, so that the scanning track of the laser beam is more suitable for the curved shape of the eyeball 94; the helical scan trajectory is more suitable for cutting scans requiring a circular or curved cross-section to be separated than the existing linear motion raster scan trajectories in the X-direction and in the Y-direction. The quick rotary motion of the rotary table 11 is convenient to realize, and the matched objective lens 30 moves linearly along the second axis b, so that the scanning device has the characteristics of high-speed scanning and high precision, can be matched with the high repetition frequency of laser pulses, can realize tissue cutting and separation in tissues such as cornea, crystalline lens and the like efficiently and quickly, shortens the laser scanning time to the maximum extent, and further improves the phenomenon that the negative pressure suction device damages fundus or loses negative pressure. Meanwhile, the scanning device utilizes the characteristic of high-speed rotation, the scanning circumferential track is smoother, the higher scanning quality is ensured, the scanning device can be applied to scenes with higher scanning quality requirements, for example, the scanning device can be applied to various eye tissue separation operations such as cornea, lens capsule, lens, vitreous body and the like, and the laser operation system has multifunction and wider application.

The object lens scanning device 10 of the ophthalmic laser in the utility model only replaces the original X-direction and Y-direction rectilinear motion in the XYZ scanner, therefore, in the process of realizing spiral scanning, the laser system is also required to be provided with an original Z-direction driving structure, the Z-direction driving structure is used for driving the rotary table 11 to move along the Z direction, or is used for driving the rectilinear motion assembly 12 to move along the Z direction relative to the rotary table 11, wherein the Z direction is parallel to the first axis a, and the Z-direction driving structure can adopt a high-speed linear motor and other structures, and can be consistent with the existing Z-direction scanning driving structure.

With continued reference to fig. 2, the scanning track of the focal point of the laser beam in this embodiment is a spiral line, when the second axis b is perpendicular to the first axis a, the objective lens 30 is driven by the optical laser objective lens scanning device 10 to move so as to form a planar spiral line, and when the objective lens 30 is driven by the optical laser objective lens scanning device 10 to move, the objective lens is synchronously driven by the Z-direction driving structure to move along a direction parallel to the first axis a, so as to form a stereoscopic spiral line attached to the surface of the cornea stroma of the eyeball 94. The incident laser beam 91 of the objective lens 30 remains vertically incident throughout the scanning process. By the adjustment of the light guide assembly 50, the laser beam 91 and the objective lens 30 keep moving synchronously, the objective lens 30 rotates around the first axis a following the turntable 11, and the linear motion assembly 12 drives the objective lens 30 to move linearly along the second axis b, thereby changing the revolution radius of the objective lens 30; it is also necessary that the Z-drive structure drives the objective lens 30 to move in the Z-direction so that the depth of the focal point of the laser beam is adjusted to the arc surface of the eyeball. By the cooperation of the above movements, the focal point of the laser beam is made to move along the spiral trajectory line.

With continued reference to fig. 2, the rotary table 11 has a cylindrical outer contour, and the first axis a is collinear with the central axis of the rotary table 11; the rotary table 11 is provided with a mounting cavity, the mounting cavity penetrates through the rotary table 11 along the direction of the first axis a, and the linear motion assembly 12 is arranged in the mounting cavity; the installation cavity is a cylindrical cavity, and the first axis a is collinear with the central axis of the installation cavity. The projection of the objective lens 30 along the direction of the first axis a falls in the corresponding circle of the installation cavity of the projection of the turntable 11 along the direction of the first axis a, so that the objective lens 30 is not overlapped with the projection entity of the turntable 11, therefore, the incident light beam of the objective lens 30 is not blocked, and the emergent light beam passing through the objective lens 30 is not blocked. Overall, the rotary table 11 is annular to adapt to the shape of the eyeball, so as to facilitate positioning relative to the eyeball. While the mounting cavity is provided for mounting the objective lens 30 on the one hand and also as a channel for the laser beam on the other hand. The linear motion assembly 12 is positioned within the mounting cavity such that the mounting cavity limits the movement of the linear motion assembly and thus the travel of the objective lens 30 along the second axis b. The second axis b is perpendicular to the first axis a; i.e., the second axis b is used as a radial direction of the turntable 11, the depth of the focal point of the laser beam is not affected during the linear motion of the objective lens 30 driven by the linear motion assembly 12.

In other alternative embodiments, the turntable 11 may be adapted to adjust its shape based on practical requirements, or may be adapted to adjust the included angle between the second axis b and the first axis a based on practical requirements, when the second axis b is not perpendicular to the first axis a, the objective lens 30 will generate a movement along a direction parallel to the first axis a during the movement along the second axis b, and at this time, the objective lens 30 needs to be driven along a direction parallel to the first axis a in cooperation with the Z direction to compensate the movement of the objective lens 30 along the direction, so that the focus of the objective lens 30 fits the eyeball.

In other alternative embodiments, the turntable 11 may be provided as a solid structure, for example, the turntable 11 is provided as a solid rotation shaft, and the linear motion assembly is connected to the outer peripheral wall of the rotation shaft and can drive the objective lens to move in the radial direction of the rotation shaft, where the turntable 11 does not block the incident beam and the outgoing beam of the objective lens 30.

The linear motion assembly 12 can move telescopically along the second axis b, one end of the linear motion assembly 12 along the first axis a is connected to the inner wall of the mounting cavity, and the other end is connected to the objective lens 30. One end of the linear motion assembly 12 is fixedly connected to the inner wall of the mounting cavity, and the cantilever end of the linear motion assembly is connected with the objective lens 30 as a telescopic end. In the process of stretching and retracting the linear motion assembly 12, the objective lens 30 is driven to move along the radial direction of the rotary table 11, and in the process of driving, the linear motion assembly 12 with the structure is adaptively stretched and retracted along with the objective lens 30 synchronously, namely, the linear motion assembly 12 does not cause shielding or interference on the objective lens 30.

The ophthalmic laser objective scanning device 10 is further configured with a driver 20, where the driver includes a first driver and a second driver, one driver is used to drive the rotary table 11 to rotate, and the second driver is used to drive the linear motion assembly 12 to stretch out and draw back, where the first driver may use a high-speed rotating motor, the high-speed rotating motor may be in transmission fit with a gear, teeth are disposed on an outer wall of the rotary table 11, and the gear is meshed with the teeth on the outer wall of the rotary table 11, so as to transmit the rotation motion of the high-speed rotating motor to the rotary table; the second driver may employ a high-speed linear motor, and the linear motion assembly 12 may be provided as a telescopic arm, and the high-speed linear motor is built in the telescopic arm to drive the telescopic arm to stretch and retract.

The controller 60 is used for controlling the driver 20, and further controlling the rotary motion of the rotary table 11 and the linear motion of the linear motion assembly 12 to match, so that the motion track of the objective lens 30 forms a spiral track matching of the focal point of the laser beam. And the controller can also be used for coordinating the coordination between the optical shutter 80 and the ophthalmic laser objective scanning device 10, when the ophthalmic laser objective scanning device 10 drives the objective lens to move to form a scanning track, the optical shutter is opened, the laser light path is conducted, and the pulse sequence generated by the laser source 40 is focused on the eyeball 94 according to a preset track; when the scanning is completed, the optical shutter is closed, and the laser light path is closed.

The controller 60 generally includes at least one processor that may communicate with a plurality of peripheral devices via a bus subsystem. These peripheral devices may include a storage system, a user interface input device, a user interface output device, and a network interface.

The network interface provides an interface to external networks and/or other devices. The network interface includes one or more interfaces known in the art, such as LAN, WLAN, bluetooth, other wired and wireless interfaces, and the like.

User interface input devices may include a keyboard, a pointing device such as a mouse, trackball, touch pad or tablet, scanner, foot pedal, joystick, touch screen embedded in a display, audio input devices such as a voice recognition system, microphone, and other types of input devices. In general, the term "input device" is intended to include a variety of conventional and proprietary devices and means for inputting information into a controller.

The user interface output device may include a display subsystem, a printer, a facsimile machine, or a non-visual display such as an audio output device. The display subsystem may be a tablet device such as a liquid crystal display, a light emitting diode display, a touch screen display, or the like. The display subsystem may also provide for non-visual displays, such as via an audio output device. In general, the term "output device" is intended to include a variety of conventional and proprietary devices and means for outputting information from the controller 60 to a user.

The storage system may store basic programming and data structures that perform the various functions of the present utility model. For example, databases and modules implementing the functionality of the methods of the present utility model may be stored in a memory system. These software modules are typically executed by a processor. In a distributed environment, software modules may be stored on and executed by processors of multiple computer systems. The storage system generally includes a memory subsystem and a file storage system. The memory subsystem typically includes a plurality of memories including a main random access memory RAM for storing instructions and data during program execution and a Read Only Memory (ROM) in which fixed instructions are stored. The file storage subsystem provides persistent non-volatile storage for program and data files. The file storage system 60 may include a hard disk drive and associated removable media, a Compact Disc (CD) drive, an optical drive, a DVD, solid state memory, and/or other removable media. One or more of these drives may be located at a remote location on the otherwise connected computer at other points of coupling with the controller 60. The modules implementing the functionality of the present utility model may be stored by a file storage system.

The bus subsystem provides a means for letting the various components and subsystems of the controller 60 communicate with each other as intended. The various subsystems and components of the controller 60 need not be in the same physical location, but may be distributed at various locations within a distributed network. The bus subsystem may be a single bus or multiple buses may be provided on demand.

The controller 60 described above is intended only as an example to illustrate only one embodiment of the present utility model. Due to the ever-changing nature of computers and networks, in other alternative embodiments, the controller 60 may also have some differences from the configuration of the controller depicted above, and will not be described in detail herein.

In other alternative embodiments, the laser system may also include other additional components. For example, spatial and/or temporal integrators may be included to control the energy distribution within the laser beam. Filters, aspirators, and other auxiliary components of a surgical laser system, etc. may also be included.

In summary, the ophthalmic laser objective scanning device includes: a rotary table 11 and a linear motion assembly 12; the rotary table 11 is rotatably provided along a first axis a passing through the rotary table 11; the linear motion assembly 12 is arranged on the rotary table 11 and rotates along with the rotary table 11, and the linear motion assembly 12 is used for installing the objective lens 30 and driving the objective lens 30 to linearly move along a second axis b relative to the rotary table 11, and the second axis b intersects with the first axis a.

So configured, the objective lens scanning device of the present utility model makes the motion track of the objective lens 30 be a rotational motion around the first axis a and a linear motion along the second axis b, which is more beneficial to forming a spiral scanning track 93, so that the scanning track of the laser beam is more adapted to the curved shape of the eyeball 94; a helical shaped scan trajectory is more suitable for a cut scan requiring a circular or curved shape in cross section to be separated than existing linear motion raster scan trajectories in the X and Y directions. The quick rotary motion of the rotary table 11 is convenient to realize, and the matched objective lens 30 moves linearly along the second axis b, so that the scanning device has the characteristics of high-speed scanning and high precision, can be matched with the high repetition frequency of laser pulses, can realize tissue cutting and separation in tissues such as cornea, crystalline lens and the like efficiently and quickly, shortens the laser scanning time to the maximum extent, and further improves the phenomenon that the negative pressure suction device damages fundus or loses negative pressure. Meanwhile, the scanning device utilizes the characteristic of high-speed rotation, the scanning circumferential track is smoother, the higher scanning quality is ensured, the scanning device can be applied to scenes with higher scanning quality requirements, for example, the scanning device can be applied to various eye tissue separation operations such as cornea, lens capsule, lens, vitreous body and the like, and the laser operation system has multifunction and wider application.

Embodiment two:

the difference between the second embodiment and the first embodiment is that the scanning track of the focal point of the laser beam in the first embodiment is spiral, so that the linear motion assembly 12 continuously drives the objective lens 30 to linearly move along the second axis b during the rotation of the turntable 11; in the second embodiment, the scanning tracks 93 of the focal point of the laser beam are concentric circles, and the linear motion assembly 12 intermittently drives the objective lens 30 to move linearly along the second axis b, so that the circular tracks are connected by radial linear tracks, and the cut corneal tissue can be peeled off entirely.

The embodiment also provides a scanning method applied to the movement of the objective lens, comprising the following steps:

generating a laser beam and guiding the laser beam to an objective lens; specifically, the laser beam may be generated by the laser source 40, and guided to the objective lens 30 by the light guide assembly 50, so that the laser beam passes through the objective lens 30 parallel to the main optical axis of the objective lens 30 and is focused at a target position, where the target position may be a corneal tissue position of the eyeball 94.

Controlling the object lens 30 to revolve around a first axis a, and controlling the object lens 30 to linearly move along the first axis a, wherein the first axis a and a second axis b intersect, and during the moving process of the object lens 30, the laser beams synchronously move, so that a plane spiral scanning track or a plane concentric circle scanning track is formed by the focus of the laser beams after passing through the object lens; in the practical application process, the objective lens is required to be synchronously driven to move along the direction parallel to the second axis b by matching with the Z-direction driving structure so as to adjust the depth position of the focal edge of the laser beam after passing through the objective lens; so that the focus of the laser beam after passing through the objective lens forms a stereoscopic spiral scanning track or a concentric circle scanning track which is adapted to the eyeball shape. Specifically, the turntable 11 may be controlled to rotate by a high-speed rotating motor, the objective lens 30 is driven to linearly move along the second axis b by a high-speed linear motor, and the objective lens 30 is driven to linearly move along the direction of the first axis a by a Z-direction linear motor, so that the focal point of the laser beam after passing through the objective lens 30 moves along a preset scanning track.

Taking the scanning track as a spiral track as an example, in the initial stage of scanning, firstly, the objective lens is controlled to be positioned at the center of the eyeball, then the optical shutter 80 is opened, the laser beam is guided by the light guide assembly and then focused to the center of the eyeball through the objective lens, the driver 20 starts to control the rotation and linear motion of the objective lens 30, the incident laser beam of the objective lens keeps synchronous motion with the objective lens, the focus of the laser beam adaptively forms a spiral scanning track which is adapted to the shape of the eyeball, and the optical shutter 80 is closed after the scanning is completed.

The scan tracks of the concentric circles are similar to the spiral scan tracks described above and will not be described again here.

The scanning method of the utility model can lead the focus of the laser beam to rapidly realize spiral or concentric scanning tracks by driving the revolution of the objective lens 30 and combining the linear motion of the objective lens, shortens the laser scanning time to the maximum extent, ensures smoother scanning circumferential tracks and ensures higher scanning quality.

The above description is only illustrative of the preferred embodiments of the present utility model and is not intended to limit the scope of the present utility model, and any changes and modifications made by those skilled in the art based on the above disclosure are intended to fall within the scope of the appended claims.

Claims (10)

1. An ophthalmic laser objective scanning device, comprising: the rotary table and the linear motion assembly;

the rotary table is rotatably arranged around a first axis, and the first axis passes through the rotary table;

the linear motion assembly is arranged on the rotary table and rotates along with the rotary table, and is used for installing an objective lens and driving the objective lens to linearly move along a second axis so as to change the distance between the objective lens and the first axis, and the second axis intersects with the first axis;

the linear motion assembly is configured to: when the objective lens is mounted on the linear motion assembly, the main optical axis of the objective lens is parallel to the first axis, and the projection of the objective lens and the turntable along the direction of the first axis is not coincident.

2. An ophthalmic laser objective scanning device as claimed in claim 1, wherein the second axis is perpendicular to the first axis.

3. An ophthalmic laser objective scanning device as claimed in claim 1, wherein the rotary stage has a mounting cavity extending through the rotary stage in a direction along the first axis, the linear motion assembly being disposed within the mounting cavity.

4. An ophthalmic laser objective scanning device as claimed in claim 1, wherein the rotary stage has a cylindrical outer contour, the first axis being collinear with a central axis of the rotary stage.

5. An ophthalmic laser objective scanning device as claimed in claim 3, wherein the mounting cavity is a cylindrical cavity, the first axis being collinear with a central axis of the mounting cavity.

6. An ophthalmic laser objective scanning device as claimed in claim 3, wherein the linear motion assembly is telescopically movable along the second axis, one end of the linear motion assembly along the first axis being connected to an inner wall of the mounting cavity, the other end being adapted to be connected to the objective lens.

7. A laser system comprising an objective lens and an ophthalmic laser objective lens scanning device according to any one of claims 1-6, said objective lens being mounted to said linear motion assembly.

8. The laser system of claim 7, further comprising a controller, a laser source, and a light guide assembly;

the laser source is used for generating a laser beam;

the light guide assembly is used for guiding the laser beam to be transmitted to the objective lens along the direction parallel to the main optical axis of the objective lens, and the laser beam forms a focus after passing through the objective lens;

the object lens scanning device of the ophthalmic laser is used for driving the object lens to move;

the controller is used for matching the movement of the objective lens with the light guide assembly so that the focus forms a spiral scanning track or a concentric circle scanning track along with the movement of the objective lens.

9. The laser system of claim 8, further comprising an energy controller disposed on a delivery path of the laser beam for varying pulse energy of the laser beam.

10. The laser system of claim 8, further comprising a shutter disposed in a transmission path of the laser beam between the laser source and the light guide assembly for controlling the on-off of the transmission path of the laser beam.

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