Ophthalmic laser system with z-direction multi-focal optics

Abstract

In certain embodiments, an ophthalmic laser system includes a laser source, a multifocal optic, scanners, a delivery optic, and a computer. The laser source generates an ultrashort laser pulse laser beam. The multifocal optic multiplexes the laser beam to create focal spots in a target along a propagation axis of the laser beam. The scanners direct the laser beam in x, y, and z directions. The delivery optic focuses the laser beam within the target to form focal spots in the target along the propagation axis of the laser beam. The computer instructs the scanners and the delivery optic to direct and focus the focal spots at the target according to a scan pattern.

Description

Technical Field

[0001] This disclosure relates generally to ophthalmic laser systems, and more specifically to ophthalmic laser systems with multifocal optics. Background Technology

[0002] Ophthalmic laser systems deliver laser pulses to focus a focal spot along a scanning pattern on a target. These laser systems have a variety of applications. For example, they can be used for surgical procedures on ophthalmic tissues. When the beam intensity or energy density exceeds a plasma or photo-rupture threshold, the laser pulse creates plasma bubbles or cavitation bubbles at the focal spot. The pattern of these bubbles can form surgical incisions or photo-rupture zones.

[0003] As another example, ophthalmic laser systems can be used to adjust light (or laser) tunable lenses (LALs). In cataract surgery, the cloudy natural lens is removed and replaced with an artificial intraocular lens (IOL). Preoperative ocular measurements are used to calculate the power and type of the IOL to optimize postoperative vision. However, due to the limited accuracy of preoperative measurements and variations in eye healing, achieving the desired visual outcome can be challenging.

[0004] Optically adjustable lenses can be adjusted after surgery to improve vision. These lenses are made of photosensitive materials whose refractive properties change in response to light. After the eye has healed, the patient's vision is tested, and a laser system is used to scan light into the patient's eye to adjust the lens. Summary of the Invention

[0005] In some embodiments, the ophthalmic laser system includes a laser source, multifocal optics, scanners, delivery optics, and a computer. The laser source generates an ultrashort laser pulse beam. The multifocal optics multiplex the laser beam to create a focal spot in a target along the beam's propagation axis. The scanners guide the laser beam in the x, y, and z directions, where the z direction is defined by the optical axis of the laser system, and the x and y directions are orthogonal to the z direction. The delivery optics focus the laser beam within the target to form a focal spot in the target along the beam's propagation axis. The computer instructs the scanners and the delivery optics to guide and focus the focal spot on the target according to a scanning pattern.

[0006] Implementations may include one, some, all, or none of the following features.

[0007] The multifocal optical device includes a diffractive optical element that enables the laser beam to be multiplexed to generate a focal spot along the propagation axis of the laser beam.

[0008] The multifocal optical device includes a holographic optical element with a high diffraction efficiency interference pattern to generate a focal spot along the propagation axis of the laser beam.

[0009] The multifocal optical device includes a computer-controlled spatial light modulator that modulates the characteristics of the laser beam to form a focal spot along the propagation axis of the laser beam.

[0010] At least two focal spots are spatially separated by a distance greater than the focal depth of the laser beam.

[0011] The target includes a lens for the eye. The lens may include an intraocular lens (IOL) or a contact lens for the eye. The computer can determine a scanning pattern for the lens for the correction of hyperopia, myopia, or astigmatism in the eye.

[0012] The target includes the lens of the eye affected by cataracts. The computer instructs the scanners and the delivery optics to guide and focus a focal spot to open the lens capsule through an incision and emulsify the cataract lens.

[0013] The target includes the cornea of ​​the eye. The computer instructs the scanners and the delivery optics to guide and focus a focal spot to create an incision in the cornea.

[0014] In some embodiments, an ophthalmic laser system includes a laser source, multifocal optics, scanners, delivery optics, and a computer. The laser source generates an ultrashort laser pulse beam. The multifocal optics multiplex the laser beam to create a focal spot in a target along the beam's propagation axis. The target includes a lens for the eye. The scanners guide the laser beam in the x, y, and z directions, where the z direction is defined by the optical axis of the laser system, and the x and y directions are orthogonal to the z direction. The delivery optics focus the laser beam within the target to form a focal spot in the target along the beam's propagation axis. The computer determines a scanning pattern for hyperopia, myopia, or astigmatism correction in the eye and instructs the scanners and the delivery optics to guide and focus the focal spot on the target according to the scanning pattern.

[0015] Implementations may include one, some, all, or none of the following features.

[0016] The multifocal optical device includes a diffractive optical element that enables the laser beam to be multiplexed to generate a focal spot along the propagation axis of the laser beam.

[0017] The multifocal optical device includes a holographic optical element with a high diffraction efficiency interference pattern to generate a focal spot along the propagation axis of the laser beam.

[0018] The multifocal optical device includes a computer-controlled spatial light modulator that modulates the characteristics of the laser beam to form a focal spot along the propagation axis of the laser beam.

[0019] In some embodiments, a method for scanning a laser beam in an ophthalmic laser system includes: generating an ultrashort laser pulse beam from a laser source; multiplexing the laser beam using multifocal optics to generate a focal spot in a target along the propagation axis of the laser beam; guiding the laser beam in the x, y, and z directions using a scanner; focusing the laser beam within the target using delivery optics to form a focal spot in the target along the propagation axis of the laser beam; and instructing the scanner and the delivery optics via a computer to guide and focus the focal spot on the target according to a scanning pattern.

[0020] Implementations may include one, some, all, or none of the following features.

[0021] The method further includes spatially spacing at least two focal spots by a distance greater than the focal depth of the laser beam.

[0022] The target includes a lens for the eye. The method further includes determining a scanning pattern for the lens using the computer for the correction of hyperopia, myopia, or astigmatism in the eye.

[0023] The target includes the lens of the eye affected by cataracts. The method further includes instructing the scanners and the delivery optics via a computer to guide and focus a focal spot to open the lens capsule through an incision and emulsify the cataract lens.

[0024] The target includes the cornea of ​​the eye. The method further includes instructing the scanners and the delivery optics via the computer to guide and focus a focal spot to form an incision in the cornea. Attached Figure Description

[0025] Figure 1 This is a block diagram of an example ophthalmic surgical laser system for performing surgery on a target.

[0026] Figure 2 It shows that it can be made by Figure 1 Example components used by the system;

[0027] Figure 3A and Figure 3B It shows that it can be made by Figure 1 Examples of multifocal diffractive optical devices used in the system;

[0028] Figure 4A and Figure 4BThis demonstrates the relationship between the spacing between focal spots F1 and F2, the cone angle of the portion of focal spot F2 that forms the beam, and the energy loss caused by the shading effect of focal spot F1 on focal spot F2; and

[0029] Figure 5 It shows that it can be made by Figure 1 The system executes an example method for forming a focal spot in the target. Detailed Implementation

[0030] Example embodiments of the disclosed devices, systems, and methods are now shown in detail with reference to the description and accompanying drawings. The specification and drawings are not intended to be exhaustive or otherwise limit the claims to the specific embodiments shown in the drawings and disclosed in the specification. Although the drawings represent possible embodiments, they are not necessarily drawn to scale, and certain features may be simplified, exaggerated, removed, or partially cut out to better illustrate the embodiments.

[0031] Generally, this disclosure relates to ophthalmic laser systems with multifocal optics. In some embodiments, the ophthalmic laser system includes multifocal optics that multiplex a laser beam to generate multiple (e.g., two, three, or more) focal spots along the beam's propagation axis. In this way, the effective laser repetition rate can be multiplied (e.g., two, three, or more times) without facing the technical challenges of increasing laser source repetition rate or scanner speed. Additionally, the spatial spacing between focal spots along the propagation axis can be selected to reduce or minimize the shadowing effect that bubbles at shallower focal spots may have on the formation of bubbles at deeper depths. Accordingly, embodiments provide solutions for increasing the effective repetition rate of ophthalmic laser systems, thereby reducing treatment time. These embodiments may be particularly useful for custom femtosecond laser-tunable lenses (FLALs), which are intraocular lenses comprising materials whose refractive index can be modified by femtosecond laser pulses.

[0032] Figure 1This is a block diagram of an example ophthalmic surgical laser system 100 for performing surgery on target 103. System 100 includes a laser source 110, a multifocal optics 107, a scanner 120, a delivery optics 130, a patient interface 140, an imaging device 150, and a laser controller 160. In an operational example, the laser source 110 generates an ultrashort laser pulse beam 101. The multifocal optics 107 multiplexes the beam 101 to generate multiple focal spots 102 along the propagation axis of the beam 101. The scanner 120 directs the focal spots of the beam 101 towards a point on target 103. The delivery optics 130 focuses the scanned beam 101 through the patient interface 140 to generate focal spots 102 in target 103 along the propagation axis of the beam 101. The imaging device 150 generates an image of target 103 during the procedure. Laser controller 160 controls laser source 110, multifocal optics 107, scanner 120, delivery optics 130, and / or imaging device 150 to generate a scanned pattern of a focal spot in target 103. In the example xyz coordinate system, the z-axis is defined by the propagation axis 109 of beam 101, and the xy plane is orthogonal to the z-axis.

[0033] System 100 includes optical components. "Optical components" refers to one or more optical elements that act on (e.g., transmit, reflect, refract, diffract, collimate, adjust, shape, focus, modulate, and / or otherwise act on) beam 101. Examples of optical elements include lenses, prisms, mirrors, diffractive optical elements (DOEs), holographic optical elements (HOEs), and spatial light modulators (SLMs). Diffractive optical elements typically have a microstructured surface relief profile that reshapes light into different distributions through diffraction. Examples of diffractive optical elements include beam splitters, pattern generators, kinoforms, beam shapers, and linear or circular gratings. Holographic optical elements are optical elements having an interference pattern generated using holographic imaging techniques. Examples of holographic optical elements include lenses, filters, beam splitters, or diffraction gratings. A spatial light modulator is a computer-controlled device that modulates one or more characteristics (e.g., amplitude, phase, and / or polarization) of a light wave in space and time. Spatial light modulators can have translucent (LCD) or reflective (LCOS) liquid crystal microdisplays.

[0034] In some embodiments, laser source 110 includes a laser engine capable of generating a beam 101 of ultrashort laser pulses (e.g., pulses in the femtosecond, picosecond, or attosecond range). In some variations, laser source 110 includes a chirped pulse amplification (CPA) laser, which may include: an oscillator for generating a femtosecond seed pulse; a stretcher for stretching the seed pulse by 10-1000 times to the picosecond range; an amplifier for amplifying the picosecond pulse; and a compressor for compressing the duration of the amplified pulse back to the femtosecond range. In some variations, laser source 110 includes a cavity-tilted regenerative amplifier laser, which may include: an oscillator, a stretcher / compressor, and an optical amplifier. Examples of laser source 110 include bulk lasers, fiber lasers, or hybrid lasers.

[0035] In some variations, the laser pulse generated by laser source 110 can have any suitable value for the following parameters, with example ranges of values ​​as follows.

[0036] (1) Pulse duration The pulse duration ranges from 10 to 5000 femtoseconds (fs), such as 100 to 200 fs, 200 to 300 fs, 300 to 400 fs, 400 to 500 fs, 500 to 800 fs, and / or 800 to 1000 fs. The pulse duration value can be selected depending on the application. For example, for cataract surgery, this value could be 400 to 800 fs. As another example, for adjusting femtosecond laser tunable lenses (FLAL), the value could be 400 to 800 fs for some lenses, or shorter for others, such as 10 to 300 fs.

[0037] (2) Energy per pulse : 0.01 to 100 microjoules (μJ), for example 0.1 to 30 μJ.

[0038] (3) repetition frequency The repetition frequency (or repetition rate) ranges from 1 kHz to 20 MHz. The repetition frequency (or repetition rate) value can be selected depending on the application. For example, for cataract surgery, this value could be 50 to 500 kHz or up to 2 MHz. As another example, for adjusting FLAL, this value can be up to 10 MHz.

[0039] (4) Focal spot interval The spacing in the xy direction is 0.01 to 10 micrometers (μm), for example, 1 to 5 μm. For the focal spot spacing in the z direction, the z-spacing can be near or greater than the focal depth of the laser beam.

[0040] (5) Average power of laserUp to 3 watts (W). The average power of a laser (equal to the repetition rate multiplied by the energy of a single pulse) may be limited by safety standards. For example, the maximum possible exposure for an ANSI laser is approximately 3W. This value depends on the focusing angle of the laser beam entering the eye.

[0041] The multifocal optics 107 described herein enables multiple propagation of a beam 101 to generate multiple focal spots 102 in a target along the propagation axis of the beam 101. The multifocal optics 107 can enable multiple propagation of the beam 101 by altering the pulses of the beam 101 to generate multiple focal spots 102, for example, by diffrying or refracting different portions of the beam to different focal spots 102, or by modulating the amplitude, phase, and / or polarization of the beam 101 to generate different focal spots 102. Examples of multifocal optics 107 include diffractive optics, holographic optics, and spatial light modulators. Diffractive optics may have a microstructured surface relief profile or a pattern with different refractive indices that alters the laser beam to form multiple focal spots along the propagation axis of the laser beam. Holographic optics may have interference patterns with high diffraction efficiency to form multiple focal spots. Spatial light modulators can modulate the amplitude, phase, and / or polarization of the laser beam to form multiple focal spots; for example, the modulator may be an electrically addressed spatial light modulator that modulates the phase. refer to Figure 3A and Figure 3B An example of the multifocal optics 107 is described in more detail.

[0042] Scanner 120 scans beam 101 in response to instructions from laser controller 160 to direct the focal spot 102 of beam 101 toward a point on target 103. Scanner 120 includes any suitable combination of xy-scanner(s) and z-scanner(s). The optical axis of laser system 100 defines the z-axis, and the xy-plane is orthogonal to the z-axis. The xy-scanner scans the focal spot 102 of beam 101 in the xy-plane, while the z-scanner scans the focal spot 102 of beam 101 in the z-direction parallel to the z-axis. Scanner 120 may include a galvanometer scanner, which is a computer-controlled electromagnetic device that rotates a mirror mounted at the end of a rotating shaft. The mirror deflects beam 101 to scan the beam in the xy-plane. Scanner 120 may also include a linear servo motor for scanning beam 101 in the z-direction.

[0043] Delivery optics 130 focuses beam 101 in response to instructions from laser controller 160 to create focal spot 102 in target 103. Delivery optics 130 may include focusing objectives, beam expanders, birefringent lenses, and other lenses to guide, collimate, adjust, and / or focus the scanned beam 101 through patient interface 140 to the focal spot 102 of target 103.

[0044] During laser surgery, the patient interface 140 can be attached to and secured to the target 103. For example, the patient interface 140 may include a one-piece or two-piece transparent flat lens that is attached to a mount on the delivery optics 130. This mount can provide a stable connection between the patient interface and the delivery optics 130.

[0045] In some embodiments, target 103 may include a specific type of artificial intraocular lens (IOL) or laser-tunable lens (LAL) (also referred to as “optically tunable lens”). An optically tunable lens is an artificial lens implanted, for example, during cataract surgery. After the eye has healed, the refractive properties of the lens can be adjusted by directing a beam 101 from outside the eye onto the lens to form a focal spot 102. The laser-tunable lens may be a femtosecond laser-tunable lens (FLAL) comprising a material whose refractive index can be modified by a femtosecond laser pulse. The laser pulse can modify the refractive index in any suitable manner. For example, the pulse can change the hydration level of the lens material (and the cornea). Increasing the hydration level decreases the refractive index, while decreasing the hydration level increases the refractive index. As another example, the pulse can change the crosslinking of the lens material (or the cornea), which alters the refractive index.

[0046] In other embodiments, target 103 may include a contact lens comprising a material whose refractive index can be modified by a femtosecond laser pulse. The laser pulse can modify the refractive index in any suitable manner, for example, as described above with reference to FLAL. The refractive power and higher-order aberrations of the contact lens can be customized according to the patient's higher-order aberrations. In these embodiments, when the contact lens is modified by the laser pulse, the contact lens is placed on a retainer, i.e., the contact lens is not on the eye.

[0047] In another embodiment, target 103 may include an eye. When the intensity or energy density exceeds the plasma or photo-rupture threshold of the eye, the laser pulse can form a plasma bubble or cavitation bubble in the eye at the focal spot 102 of beam 101. For example, in cataract surgery, focal spot 102 can form an incision in the cornea and / or capsule to access the cataract lens of the eye. Focal spot 102 can also emulsify the cataract lens, and multiple focal spots can reduce lens breakage time. As another example, in refractive surgery, focal spot 102 can form an incision (e.g., a flap, microgroove, or other incision) or other pattern in the cornea to alter the refractive properties of the cornea.

[0048] Imaging device 150 receives imaging light 104 and generates a real-time image of target 103 during surgery. Imaging device 150 can generate image data 105 and send data 105 to laser controller 160. Examples of imaging device 150 include surgical microscopes, video microscopes, digital microscopes, ophthalmoscopes, optical coherence tomography (OCT) imaging systems, and / or cameras.

[0049] The laser controller 160 is a computer that includes a memory M storing instructions executable by a processor P to control the pulsed laser source 110, multifocal optics 107, scanner 120, delivery optics 130, and / or imaging device 150. Typically, the processor of the laser controller 160 includes one or more CPUs (such as CPUs manufactured by Intel, AMD, and other companies), microprocessors, field-programmable gate arrays (FPGAs), application-specific integrated circuits (ASICs), digital signal processors (DSPs), or system-on-a-chip (SoC) processors communicatively coupled to the memory. The memory may include non-transitory computer-readable media and may include volatile or non-volatile memory, including magnetic media, optical media, random access memory (RAM), read-only memory (ROM), removable media, or similar components. The memory may store software instructions executable by the processor to generate control signals 106 that control the operation of the pulsed laser source 110, scanner 120, delivery optics 130, and imaging device 150.

[0050] In some embodiments, the laser controller 160 generates a signal 106 to control parameters of the beam 101 generated by the pulsed laser source 110, such as repetition rate, pulse length, and pulse energy. The laser controller 160 also generates a signal 106 to instruct the multifocal optics 107, the scanner 120, and / or the delivery optics 130 to guide and focus the focal spot 102 according to the scanning pattern. The scanning pattern can be any suitable two-dimensional or three-dimensional shape or pattern, including spiral, raster, sawtooth, circular, elliptical, or cylindrical patterns.

[0051] The laser controller 160 can determine the scanning pattern based on the operational purpose. In some embodiments, the scanning pattern can be used to adjust the refractive properties of an optically tunable lens. For example, the scanning pattern can form a focal spot 102 in the optically tunable lens to change the lens's refractive properties. The laser controller 160 can determine the scanning pattern based on the type of correction. For hyperopia or myopia correction, the refractive properties can be altered to produce an artificial lens that guides light onto the retina of the eye. For example, to treat hyperopia, the refractive index can be increased in the central region and / or decreased in the peripheral region. To treat myopia, the refractive index can be decreased in the central region and / or increased in the peripheral region.

[0052] The central region can be described by a diameter that is a percentage of the total lens diameter, where the percentage value is in the range of, for example, 2% to 5%, 5% to 10%, 10% to 25%, and / or 25% to 50%. For example, if the percentage is 10%, the central region is described by a diameter that is 10% of the total lens diameter. The peripheral region can be an annular zone, where the outer ring can be described by a diameter r1 that is a percentage of the total lens diameter, and the inner ring can be described by a diameter d2 that is also a percentage of the total lens diameter, but d2 < d1. The percentage value can be in the range of, for example, 60% to 70%, 70% to 80%, 80% to 90%, and / or 90% to 99%.

[0053] For astigmatism correction, the focal spot 102 can be formed as a band across the lens. The band can have any suitable size and shape to compensate for the refractive error of the eye, which can be determined by, for example, an aberrometer or a corneal topographer.

[0054] In other embodiments, the scanning pattern can be used for eye surgery. For example, in cataract surgery, the scanning pattern guides the focal spot 102 to form incisions in the cornea and / or the capsule to access the lens of the eye. The scanning pattern can also guide the focal spot 102 to open the lens capsule with a circular incision and emulsify the cataractous lens. As another example, in refractive surgery, the scanning pattern guides the focal spot 102 to form incisions (e.g., flaps, microgrooves, or other incisions) or other patterns in the cornea to change the refractive properties of the cornea.

[0055] Figure 2 An example of components that can be used by Figure 1 system 100 is shown. In the illustrated embodiment, system 100 includes a laser source 110, beam conditioning optics 172, multifocal optics 107, a scanner 120, and delivery optics 130 to generate focal spots 102 (102a, 102b, 102c). In the illustrated example, the delivery optics includes guiding optics 176 and a focusing objective 178.

[0056] In the illustrated example, beam-adjusting optics 172 adjusts beam 101, such as expanding and / or collimating it. Beam-adjusting optics 172 may include, for example, expanders and / or collimators. Multifocal optics 107 multiplexes beam 101 to produce multiple focal spots 102 in a target along the propagation axis 109 of beam 101. Guiding optics 176 directs beam 101 toward a focusing objective 178, which focuses beam 101 onto the focal spots 102. In the illustrated example, guiding optics 176 may be a mirror that directs beam 101 toward the focusing objective 178. Note that even if guiding optics 176 changes the direction of beam 101, the focal spots remain positioned along the propagation axis 109 of beam 101. In other examples, guiding optics 176 may transmit or refract beam 101, or may be omitted.

[0057] Figure 3A and Figure 3B It shows that it can be made by Figure 1 An example of the multifocal diffractive optical device 107 used in system 100. Figure 3A A multifocal optics device 107 is shown, which includes Fresnel lenses with diffraction patterns to produce focal spots 102: +2, +1, 0, -1, and -2.

[0058] Figure 3B A multifocal optics device 107 is shown, which includes a phase modulator (e.g., a phase plate with a diffraction pattern) and a focusing lens to produce focal spots 102: +2, +1, 0, -1, and -2. The phase modulator may be a diffractive optical element, a holographic optical element, or a spatial light modulator.

[0059] Figure 4A and Figure 4B The relationship between the spacing S between the focal spots 102 (F1, F2) along the propagation axis 109, the cone angle A of the portion of the bundle 101 that forms the focal spot F2, and the energy loss caused by the shading effect of the focal spot F1 on the focal spot F2 is shown. Figure 4A A view showing the multifocal optics 107 and the focal spots F1 and F2 along the propagation axis 109 is presented. Figure 4B A view of plane 111 as seen from focal spot F2 is shown.

[0060] In some targets 103 (e.g., target 103 is part of an eye), plasma bubbles formed by the focal spot F1 may block the beam energy directed to the focal spot F2, resulting in energy loss at the focal spot F2. In some targets 103 (e.g., target 103 is an optically tunable lens), no plasma bubbles form at the focal spot F1, so this type of energy loss is not a concern.

[0061] Although the parameters in the example shown can have any suitable values, specific values ​​have been assigned to facilitate the description of the relationship. In this example, the portion of the beam forming focal spot F2 forms a cone with a cone angle A of any suitable value (e.g., 0.1 to 0.2 radians, such as 0.15 radians). The spacing S between focal spots F1 and F2 can have any suitable value; for example, the spacing can be greater than the focal depth of the laser beam, such as 5 to 50 micrometers (μm), 50 to 100 μm, 100 to 300 μm, 300 to 500 μm, and / or greater than 500 μm, such as 200 μm. The diameter d of the plasma bubble formed by focal spot F1... p1 It can be any suitable value, such as 2 to 5 μm, like 3 μm.

[0062] In the example shown, the focal spot F1 is closer to the transport optics 130 than the focal spot F2, i.e., focal spot F1 is shallower than focal spot F2, or focal spot F2 is deeper than focal spot F1. In some cases, the plasma bubble formed by focal spot F1 may block the beam energy directed to focal spot F2, resulting in energy loss at focal spot F2. In this case, the spacing S between focal spots F1 and F2 can be selected so that the energy loss caused by the blocking effect of focal spot F1 on focal spot F2 is negligible. Generally, increasing the spacing S between focal spots F1 and F2 and / or increasing the cone angle A of the beam forming focal spot F2 reduces the energy loss caused by the blocking effect of focal spot F1 on focal spot F2.

[0063] The diameter d of the cone forming the focal spot F2, measured at a plane 111 orthogonal to the propagation axis 109 (where the focal spot F1 intersects the propagation axis 109). b2 It can be calculated based on angle A and interval S:

[0064] d b2 = 2 × angle A × interval S = 2 × 0.15 × 200 μm = 60 μm

[0065] The amount of shading can be measured by the shading ratio R:

[0066] R=(d p1 / d b2 ) 2 = (3μm / 60μm) 2 =1 / 400 = 0.0025 = 0.25%

[0067] Energy loss E L The following can be calculated based on the shading ratio R:

[0068] E L =R=0.25%

[0069] In some embodiments, such as in cataract or refractive surgery, a 0.25% energy loss may be considered acceptable. The maximum acceptable energy loss P may depend on the type of surgery.

[0070] Figure 5 It shows that it can be made by Figure 1 The system 100 performs an example method for forming a focal spot 102 in a target 103. The focal spot 102 is formed along the propagation axis 109 of the laser beam 101.

[0071] The method begins at step 310, where system 100 determines a scanning pattern. The scanning pattern can be used to adjust an optically tunable lens or to perform surgery on ophthalmic tissues (e.g., the lens or cornea). In some embodiments, as shown with reference to FIG4, laser controller 106 determines a scanning pattern that satisfies a maximum acceptable energy loss P, the scanning pattern having a cone angle A and a spacing S between the focal spot.

[0072] In step 312, laser source 110 generates laser beam 101. In step 314, beam-adjusting optics 172 adjusts beam 101. In step 316, multifocal optics 107 multiplexes beam 101 to generate a focal spot along the propagation axis 109 of beam 101. In step 318, scanner 120 scans beam 101 according to a scanning pattern. In step 320, delivery optics 130 focuses beam 101 to form a focal spot 102 in target 103. The method then ends.

[0073] Components of the systems and devices disclosed herein (such as laser controller 160) may include interfaces, logic, and / or memory, any of which may include computer hardware and / or software. Interfaces may receive input to a component and / or send output from a component, and are typically used to exchange information between, for example, software, hardware, peripherals, users, and combinations thereof. A user interface (e.g., a graphical user interface (GUI)) is a type of interface that a user can use to interact with a computer. Examples of user interfaces include displays, touchscreens, keyboards, mice, gesture sensors, microphones, and speakers.

[0074] Logic can perform operations on components. Logic may include one or more electronic devices that process data (e.g., execute instructions to generate outputs from inputs). Examples of such electronic devices include computers, processors, microprocessors (e.g., central processing units (CPUs)), and computer chips. Logic may include computer software that encodes instructions that can be executed by electronic devices to perform operations. Examples of computer software include computer programs, applications, and operating systems.

[0075] Memory can store information and may include tangible, computer-readable, and / or computer-executable storage media. Examples of memory include computer memory (e.g., random access memory (RAM) or read-only memory (ROM)), mass storage media (e.g., hard disk), removable storage media (e.g., optical disc (CD) or digital video or universal disc (DVD)), databases, network storage devices (e.g., servers), and / or other computer-readable media. Specific embodiments may be directed to memory encoded with computer software.

[0076] Although this disclosure has been described with reference to certain embodiments, modifications to the embodiments (such as alterations, substitutions, additions, omissions, and / or other modifications) will be apparent to those skilled in the art. Accordingly, modifications can be made to the embodiments without departing from the scope of the invention. For example, modifications can be made to the systems and devices disclosed herein. Components of the systems and devices may be integral or separate, or the operation of the systems and devices may be performed by more, fewer, or other components, as will be apparent to those skilled in the art. As another example, modifications can be made to the methods disclosed herein. These methods may include more, fewer, or other steps, and these steps may be performed in any suitable order, as will be apparent to those skilled in the art.

[0077] To assist the Patent Office and readers in interpreting the claims, the applicant notes that they do not intend for any claim or claim element to invoke 35 U.SC §112(f) unless the terms “means for…” or “steps for…” are expressly used in a particular claim. The applicant understands that the use of any other terms in the claims (e.g., “mechanism,” “module,” “device,” “unit,” “component,” “element,” “building block,” “device,” “machine,” “system,” “processor,” or “controller”) refers to structures known to a person skilled in the art and is not intended to invoke 35 U.SC §112(f).

Claims

1. An ophthalmic laser system comprising: a laser source configured to generate a laser beam of ultra-short laser pulses to perform a procedure on an eye; a multi-focal optic configured to multi-path the laser beam to create a plurality of focal spots in a target along a propagation axis of the laser beam, the plurality of focal spots including a first focal spot and a second focal spot, the first focal spot being closer to the multi-focal optic than the second focal spot along the propagation axis of the laser beam; a plurality of scanners configured to direct the laser beam in an x-direction, a y-direction, and a z-direction, the z-direction being defined by an optical axis of the laser system, the x-direction and the y-direction being orthogonal to the z-direction; a delivery optic configured to focus the laser beam within the target to form the plurality of focal spots in the target along the propagation axis of the laser beam; and a computer configured to: determine a maximum acceptable energy loss for an energy loss due to a shadowing effect of the first focal spot on the second focal spot in accordance with the procedure; determine a scan pattern for the plurality of focal spots having a spatial separation along the propagation axis of the laser beam that keeps the energy loss below the maximum acceptable energy loss; instruct the scanners and the delivery optic to direct and focus the plurality of focal spots at the target in accordance with the scan pattern; and simultaneously form the plurality of focal spots within the target along the propagation axis with the spatial separation between the first focal spot and the second focal spot.

2. The ophthalmic laser system of claim 1, the multi-focal optic comprising a diffractive optical element that multi-paths the laser beam to create the plurality of focal spots along the propagation axis of the laser beam.

3. The ophthalmic laser system of claim 1, the multi-focal optic comprising a holographic optical element having an interference pattern of high diffraction efficiency to create the plurality of focal spots along the propagation axis of the laser beam.

4. The ophthalmic laser system of claim 1, the multi-focal optic comprising a computer-controlled spatial light modulator that modulates a characteristic of the laser beam to form the plurality of focal spots along the propagation axis of the laser beam.

5. The ophthalmic laser system of claim 1, at least two of the focal spots being spatially separated by a distance greater than a focal depth of the laser beam.

6. The ophthalmic laser system of claim 1, the target comprising a lens for an eye.

7. The ophthalmic laser system of claim 6, the lens comprising an intraocular lens (IOL) for the eye.

8. The ophthalmic laser system of claim 6, the lens comprising a contact lens for the eye.

9. The ophthalmic laser system of claim 6, the computer configured to: determine the scan pattern for the lens for a hyperopic, myopic, or astigmatic correction of the eye.

10. The ophthalmic laser system of claim 1: ​ The target includes a cataract lens of an eye; and The computer is configured to instruct the scanner and the delivery optics to direct and focus the multiple focal spots to simultaneously: open a lens capsule through an incision; and emulsify the cataract lens.

11. The ophthalmic laser system of claim 1: The target includes a cornea of an eye; and The computer is configured to instruct the scanner and the delivery optics to direct and focus the multiple focal spots to form an incision in the cornea.

12. An ophthalmic laser system, comprising: a laser source configured to generate a laser beam of ultra-short laser pulses to perform a surgery on an eye; a multi-focal optic configured to multi-path the laser beam to create multiple focal spots in a target along a propagation axis of the laser beam, the multiple focal spots including a first focal spot and a second focal spot, the target including a lens for an eye, the first focal spot being closer to the multi-focal optic than the second focal spot along the propagation axis of the laser beam; a plurality of scanners configured to direct the laser beam in an x-direction, a y-direction, and a z-direction, the z-direction being defined by an optical axis of the laser system, the x-direction and the y-direction being orthogonal to the z-direction; a delivery optic configured to focus the laser beam within the target to form the multiple focal spots in the target along the propagation axis of the laser beam; and a computer configured to: determine a maximum acceptable energy loss for an energy loss due to a shadowing effect of the first focal spot on the second focal spot in accordance with the surgery; determine a scan pattern of the multiple focal spots having a spatial separation along the propagation axis of the laser beam that keeps the energy loss below the maximum acceptable energy loss, the scan pattern being for a hyperopia, myopia, or astigmatism correction of the eye; instruct the scanners and the delivery optic to direct and focus the multiple focal spots in accordance with the scan pattern; and simultaneously form the multiple focal spots within the target along the propagation axis with the spatial separation between the first focal spot and the second focal spot.

13. The ophthalmic laser system of claim 12, the multi-focal optic including a diffractive optical element that multi-paths the laser beam to create the multiple focal spots along the propagation axis of the laser beam.

14. The ophthalmic laser system of claim 12, the multi-focal optic including a holographic optical element having an interference pattern of high diffraction efficiency to create the multiple focal spots along the propagation axis of the laser beam.

15. The ophthalmic laser system of claim 12, the multi-focal optic including a computer-controlled spatial light modulator that modulates a characteristic of the laser beam to form the multiple focal spots along the propagation axis of the laser beam. ​

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