Patent Description:
Vision impairments such as myopia (near-sightedness), hyperopia and astigmatism can be corrected using eyeglasses or contact lenses. Alternatively, the cornea of the eye can be reshaped surgically to provide the needed optical correction. Eye surgery has become commonplace with some patients pursuing it as an elective procedure to avoid using contact lenses or glasses to correct refractive problems, and others pursuing it to correct adverse conditions such as cataracts. And, with recent developments in laser technology, laser surgery is becoming the technique of choice for ophthalmic procedures.

Different laser eye surgical systems use different types of laser beams for the various procedures and indications. These include, for instance, ultraviolet lasers, infrared lasers, and near-infrared, ultra-short pulsed lasers. Ultra-short pulsed lasers emit radiation with pulse durations as short as <NUM> femtoseconds and as long as <NUM> nanoseconds, and a wavelength between <NUM> and <NUM>.

Prior surgical approaches for reshaping the cornea include laser assisted in situ keratomileusis (hereinafter "LASIK"), photorefractive keratectomy (hereinafter "PRK") and Small Incision Lens Extraction (hereinafter "SmILE").

In the LASIK procedure, an ultra-short pulsed laser is used to cut a corneal flap to expose the corneal stroma for photoablation with ultraviolet beams from an excimer laser. Photoablation of the corneal stroma reshapes the cornea and corrects the refractive condition such as myopia, hyperopia, astigmatism, and the like. In a PRK procedure where no flap is created, the epithelium layer is first removed, and some stroma material is then removed by an excimer laser. The epithelium layer will grow back within a few days after the procedure.

In the SmILE procedure, instead of ablating corneal tissue with an excimer laser following the creation of a corneal flap, the technique involves tissue removal with two femtosecond laser incisions that intersect to create a lenticule for extraction. The extraction of the lenticule changes the shape of the cornea and its optical power to accomplish vision correction. Lenticular extractions can be performed either with or without the creation of a corneal flap. With the flapless procedure, a refractive lenticule is created in the intact portion of the anterior cornea and removed through a small incision.

<CIT> discloses ophthalmic laser procedures and, more particularly, to systems and methods for lenticular laser incision. An ophthalmic surgical laser system comprises a laser delivery system for delivering a pulsed laser beam to a target in a subject's eye, an XY-scan device to deflect the pulsed laser beam, a Z-scan device to modify a depth of a focus of the pulsed laser beam, and a controller configured to form a top lenticular incision and a bottom lenticular incision of a lens in the subject's eye.

The present invention provides an ophthalmic surgical laser system which includes: a laser delivery system for delivering a pulsed laser beam to a target in a subject's eye; a high frequency scanner to scan the pulsed laser beam back and forth at a predefined frequency; an XY-scanner to deflect the pulsed laser beam, the XY-scanner being separate from the high frequency scanner; a Z-scanner to modify a depth of a focus of the pulsed laser beam; and a controller configured to control the high frequency scanner, the XY-scanner and the Z-scanner to successively form a plurality of sweeps which collectively form at least one lenticular incision of a lens in the subject's eye, the lens having a curved surface that defines an apex and a Z axis passing through the apex, wherein each sweep is formed by: controlling the high frequency scanner to deflect the pulsed laser beam to form a scan line, the scan line being a straight line having a predefined length and being tangential to a parallel of latitude of the lens, the parallel of latitude being a circle on the surface of the lens that is perpendicular to the Z axis and has a defined distance to the apex, and controlling the XY-scanner and the Z-scanner to move the scan line along a meridian of longitude of the lens, the meridian of longitude being a curve that passes through the apex and has a defined angular position around the Z axis, wherein a sweeping speed of moving the scan line along the meridian of longitude varies with a position of the scan line along the meridian of longitude, wherein the sweeping speed is higher when the scan line passes through the apex than when the scan line is at an edge of the lenticular incision, wherein the plurality of sweeps are successively formed one after another along the respective meridians of longitude which are different from one another.

In another aspect, the present invention provides an ophthalmic surgical laser system which includes: a laser delivery system for delivering a pulsed laser beam to a target in a subject's eye; a high frequency scanner to scan the pulsed laser beam back and forth at a predefined frequency; an XY-scanner to deflect the pulsed laser beam, the XY-scanner being separate from the high frequency scanner; a Z-scanner to modify a depth of a focus of the pulsed laser beam; and a controller configured to control the high frequency scanner, the XY-scanner and the Z-scanner to successively form a plurality of sweeps which collectively form at least one lenticular incision of a lens in the subject's eye, the lens having a curved surface that defines an apex and a Z axis passing through the apex, wherein each sweep is formed by: controlling the high frequency scanner to deflect the pulsed laser beam to form a scan line, the scan line being a straight line having a predefined length and being tangential to a parallel of latitude of the lens, the parallel of latitude being a circle on the surface of the lens that is perpendicular to the Z axis and has a defined distance to the apex, controlling the XY-scanner and the Z-scanner to move the scan line along a meridian of longitude of the lens, the meridian of longitude being a curve that passes through the apex and has a defined angular position around the Z axis, and controlling the laser delivery system to vary a laser pulse energy during each sweep to use a lower laser pulse energy when the scan line is located within a vicinity of the apex of the lenticule than when the scan line is located at an edge of the lenticule, wherein the plurality of sweeps are successively formed one after another along the respective meridians of longitude which are different from one another.

This summary and the following detailed description are merely exemplary, illustrative, and explanatory, and are not intended to limit, but to provide further explanation of the invention as claimed. Additional features and advantages of the invention will be set forth in the descriptions that follow, and in part will be apparent from the description, or may be learned by practice of the invention. The objectives and other advantages of the invention will be realized and attained by the structure particularly pointed out in the written description, claims and the appended drawings.

A better understanding of the features and advantages will be facilitated by referring to the following detailed description that sets forth illustrative embodiments using principles of the invention, as well as to the accompanying drawings, in which like numerals refer to like parts throughout the different views. Like parts, however, do not always have like reference numerals. Further, the drawings are not drawn to scale, and emphasis has instead been placed on illustrating the principles of the invention. All illustrations are intended to convey concepts, where relative sizes, shapes, and other detailed attributes may be illustrated schematically rather than depicted literally or precisely.

Embodiments of this invention are generally directed to systems for laser-assisted ophthalmic procedures, and more particularly, to systems for corneal lenticule incision.

Referring to the drawings, <FIG> shows a system <NUM> for making an incision in a material <NUM>. The system <NUM> includes, but is not limited to, a laser <NUM> capable of generating a pulsed laser beam <NUM>, an energy control module <NUM> for varying the pulse energy of the pulsed laser beam <NUM>, a Z-scanner <NUM> for modifying the depth of the pulse laser beam <NUM>, a controller <NUM>, a prism <NUM> (e.g., a Dove or Pechan prism, or the like), and an XY-scanner <NUM> for deflecting or directing the pulsed laser beam <NUM> from the laser <NUM> on or within the material <NUM>. The controller <NUM>, such as a processor operating suitable control software, is operatively coupled with the Z-scanner <NUM>, the XY-scanner <NUM>, and the energy control unit <NUM> to direct a scan line <NUM> of the pulsed laser beam along a scan pattern on or in the material <NUM>. The system <NUM> further includes a beam splitter <NUM> and a detector <NUM> coupled to the controller <NUM> for a feedback control mechanism (not shown) of the pulsed laser beam <NUM>. Other feedback methods may also be used, including but not necessarily limited to position encoder on the scanner <NUM>, or the like. The pattern of pulses may be summarized in machine readable data of tangible storage media in the form of a treatment table. The treatment table may be adjusted according to feedback input into the controller <NUM> from an automated image analysis system in response to feedback data provided from an ablation monitoring system feedback system (not shown). Optionally, the feedback may be manually entered into the controller <NUM> by a system operator. The feedback may also be provided by integrating a wavefront measurement system (not shown) with the laser surgery system <NUM>. The controller <NUM> may continue and/or terminate a sculpting or incision in response to the feedback, and may also modify the planned sculpting or incision based at least in part on the feedback. Measurement and imaging systems are further described in <CIT> and <CIT>.

The system <NUM> uses a pair of scanning mirrors or other optics (not shown) to angularly deflect and scan the pulsed laser beam <NUM>. For example, scanning mirrors driven by galvanometers may be employed where each of the mirrors scans the pulsed laser beam <NUM> along one of two orthogonal axes. A focusing objective (not shown), whether one lens or several lenses, images the pulsed laser beam <NUM> onto a focal plane of the system <NUM>. The focal point of the pulsed laser beam <NUM> may thus be scanned in two dimensions (e.g., the x-axis and the y-axis) within the focal plane of the system <NUM>. Scanning along the third dimension, i.e., moving the focal plane along an optical axis (e.g., the z-axis), may be achieved by moving the focusing objective, or one or more lenses within the focusing objective, along the optical axis.

Laser <NUM> may comprise a femtosecond laser capable of providing pulsed laser beams, which may be used in optical procedures, such as localized photodisruption (e.g., laser induced optical breakdown). Localized photodisruptions can be placed at or below the surface of the material to produce high-precision material processing. For example, a micro-optics scanning system may be used to scan the pulsed laser beam to produce an incision in the material, create a flap of the material, create a pocket within the material, form removable structures of the material, and the like. The term "scan" or "scanning" refers to the movement of the focal point of the pulsed laser beam along a desired path or in a desired pattern.

The laser <NUM> may comprise a laser source configured to deliver an ultraviolet laser beam comprising a plurality of ultraviolet laser pulses capable of photodecomposing one or more intraocular targets within the eye.

Although the laser system <NUM> may be used to photoalter a variety of materials (e.g., organic, inorganic, or a combination thereof), the laser system <NUM> is suitable for ophthalmic applications. In these cases, the focusing optics direct the pulsed laser beam <NUM> toward an eye (for example, onto or into a cornea) for plasma mediated (for example, non-UV) photoablation of superficial tissue, or into the stroma of the cornea for intrastromal photodisruption of tissue. The surgical laser system <NUM> may also include a lens to change the shape (for example, flatten or curve) of the cornea prior to scanning the pulsed laser beam <NUM> toward the eye.

The laser system <NUM> is capable of generating the pulsed laser beam <NUM> with physical characteristics similar to those of the laser beams generated by a laser system disclosed in <CIT>, <CIT>, and <CIT>.

<FIG> shows another exemplary diagram of the laser system <NUM>. <FIG> shows components of a laser delivery system including a moveable XY-scanner (or XY-stage) <NUM> of a miniaturized femtosecond laser system. The system <NUM> may use a femtosecond oscillator, or a fiber oscillator-based low energy laser. This allows the laser to be made much smaller. The laser-tissue interaction is in the low-density-plasma mode. An exemplary set of laser parameters for such lasers include pulse energy in the <NUM>-<NUM> nJ range and pulse repetitive rates (or "rep rates") in the <NUM>-<NUM> range. A fast-Z scanner <NUM> and a resonant scanner <NUM> direct the laser beam <NUM> to the prism <NUM>. When used in an ophthalmic procedure, the system <NUM> also includes a patient interface <NUM> design that has a fixed cone nose and a portion that engages with the patient's eye. A beam splitter is placed inside the cone of the patient interface to allow the whole eye to be imaged via visualization optics. The system <NUM> may use: optics with a <NUM> numerical aperture (NA) which would produce <NUM> Full Width at Half Maximum (FWHM) focus spot size; and a resonant scanner <NUM> that produces <NUM>-<NUM> scan line with the XY-scanner scanning the resonant scan line to a <NUM> field. The prism <NUM> rotates the resonant scan line in any direction on the XY plane. The fast-Z scanner <NUM> sets the incision depth and produces a side cut. The system <NUM> may also include an auto-Z module <NUM> to provide depth reference. The miniaturized femtosecond laser system <NUM> may be a desktop system so that the patient sits upright while being under treatment. This eliminates the need of certain opto-mechanical arm mechanism(s), and greatly reduces the complexity, size, and weight of the laser system. Alternatively, the miniaturized laser system may be designed as a conventional femtosecond laser system, where the patient is treated while lying down.

<FIG> illustrates a simplified block diagram of an exemplary controller <NUM> that may be used by the laser system <NUM> to control the laser system <NUM> and execute at least some of the steps discussed in detail below. Controller <NUM> typically includes at least one processor <NUM> which may communicate with a number of peripheral devices via a bus subsystem <NUM>. These peripheral devices may include a storage subsystem <NUM>, comprising a memory subsystem <NUM> and a file storage subsystem <NUM>, user interface input devices <NUM>, user interface output devices <NUM>, and a network interface subsystem <NUM>. Network interface subsystem <NUM> provides an interface to outside networks <NUM> and/or other devices. Network interface subsystem <NUM> includes one or more interfaces known in the arts, such as LAN, WLAN, Bluetooth, other wire and wireless interfaces, and so on.

User interface input devices <NUM> may include a keyboard, pointing devices such as a mouse, trackball, touch pad, or graphics tablet, a scanner, foot pedals, a joystick, a touch screen incorporated into a display, audio input devices such as voice recognition systems, microphones, and other types of input devices. In general, the term "input device" is intended to include a variety of conventional and proprietary devices and ways to input information into controller <NUM>.

The display subsystem may be a flat-panel device such as a liquid crystal display (LCD), a light emitting diode (LED) display, a touchscreen display, or the like. The display subsystem may also provide a non-visual display such as via audio output devices. In general, the term "output device" is intended to include a variety of conventional and proprietary devices and ways to output information from controller <NUM> to a user.

Storage subsystem <NUM> can store the basic programming and data constructs that provide the functionality of the various user interface output devices <NUM>. For example, a database and modules implementing the functionality of the methods as described herein, may be stored in storage subsystem <NUM>. These software modules are generally executed by processor <NUM>. In a distributed environment, the software modules may be stored on a plurality of computer systems and executed by processors of the plurality of computer systems. Storage subsystem <NUM> typically comprises memory subsystem <NUM> and file storage subsystem <NUM>.

Memory subsystem <NUM> typically includes a number of memories including a main random access memory (RAM) <NUM> for storage of instructions and data during program execution and a read only memory (ROM) <NUM> in which fixed instructions are stored. File storage subsystem <NUM> provides persistent (non-volatile) storage for program and data files. File storage subsystem <NUM> may include a hard disk drive along with associated removable media, a Compact Disk (CD) drive, an optical drive, DVD, solid-state memory, and/or other removable media. One or more of the drives may be located at remote locations on other connected computers at other sites coupled to controller <NUM>. The modules implementing the functionality of the present invention may be stored by file storage subsystem <NUM>.

Bus subsystem <NUM> provides a mechanism for letting the various components and subsystems of controller <NUM> communicate with each other as intended. The various subsystems and components of controller <NUM> need not be at the same physical location but may be distributed at various locations within a distributed network. Although bus subsystem <NUM> is shown schematically as a single bus, alternate embodiments of the bus subsystem may utilize multiple busses.

Due to the ever-changing nature of computers and networks, the description of controller <NUM> depicted in <FIG> is intended only as an example for purposes of illustrating only one exemplary controller. Many other configurations of controller <NUM>, having more or fewer components than those depicted in <FIG>, are possible.

As should be understood by those of skill in the art, additional components and subsystems may be included with laser system <NUM>. For example, spatial and/or temporal integrators may be included to control the distribution of energy within the laser beam. Ablation effluent evacuators/filters, aspirators, and other ancillary components of the surgical laser system are known in the art, and may be included in the system. In addition, an imaging device or system may be used to guide the laser beam.

The laser surgery system <NUM> may include a femtosecond oscillator-based laser operating in the MHz range, for example, <NUM>, for example, from several MHz to tens of MHz. For ophthalmic applications, the XY-scanner <NUM> may utilize a pair of scanning mirrors or other optics (not shown) to angularly deflect and scan the pulsed laser beam <NUM>. For example, scanning mirrors driven by galvanometers may be employed, each scanning the pulsed laser beam <NUM> along one of two orthogonal axes. A focusing objective (not shown), whether one lens or several lenses, images the pulsed laser beam onto a focal plane of the laser surgery system <NUM>. The focal point of the pulsed laser beam <NUM> may thus be scanned in two dimensions (e.g., the X-axis and the Y-axis) within the focal plane of the laser surgery system <NUM>. Scanning along a third dimension, i.e., moving the focal plane along an optical axis (e.g., the Z-axis), may be achieved by moving the focusing objective, or one or more lenses within the focusing objective, along the optical axis. It is noted that in many laser surgery systems, the XY-scanner <NUM> deflects the pulse laser beam <NUM> to form a scan line. This is otherwise referred to as point-to-point scanning.

The beam scanning can be realized with a "fast-scan-slow-sweep" scanning scheme, also referred herein as a fast-scan line scheme. The scheme consists of two scanning mechanisms: first, a high frequency fast scanner is used to scan the beam back and forth to produce a short, fast scan line (e.g., a resonant scanner <NUM> of <FIG>); second, the fast scan line is slowly swept by much slower X, Y, and Z scan mechanisms. <FIG> illustrates a scanning example of a laser system <NUM> using an <NUM> (e.g. between <NUM> and <NUM>) resonant scanner <NUM> to produce a fast scan line <NUM> of about <NUM> (e.g., between <NUM> and <NUM>) and a scan speed of about <NUM>/sec, and X, Y, and Z scan mechanisms with the scan speed (sweep speed) smaller than about <NUM>/sec, or a variable sweep speed as described in more detail later. The fast scan line <NUM> may be perpendicular to the optical beam propagation direction, i.e., it is always parallel to the XY plane. The trajectory of the slow sweep <NUM> can be any three dimensional curve drawn by the X, Y, and Z scanning devices (e.g., XY-scanner <NUM> and Z-scanner <NUM>). An advantage of the "fast-scan-slow-sweep" scanning scheme is that it only uses small field optics (e.g., a field diameter of <NUM>) which can achieve high focus quality at relatively low cost. The large surgical field (e.g., a field diameter of <NUM> or greater) is achieved with the XY-scanner, which may be unlimited.

In a preferred laser system shown in <FIG> and 7A-7B, the laser system <NUM> creates a smooth lenticular cut using the "fast-scan-slow-sweep" scanning scheme under a preferred procedure. First, in a three dimensional lenticular cut, the fast scan line is preferably placed tangential to the parallels of latitude <NUM> on the surface of the lenticule. A parallel of latitude is the intersection of the surface with a plane perpendicular to the Z axis (which is the axis parallel to the depth direction of the eye), i.e. a circle on the surface of the lens that is perpendicular to the Z axis and has a defined distance to the apex (the highest point in the Z direction). For example, in the miniaturized flap maker laser system <NUM> of <FIG>, this can be realized by adjusting a prism <NUM> to the corresponding orientations via software, e.g., via the controller <NUM>. Second, the slow sweep trajectory preferably moves along the meridians of longitude <NUM> on the surface of the lenticule. A meridian of longitude is the intersection of the surface with a plane that passes through the Z axis, i.e. a curve that passes through the apex and has a defined angular direction with respect to the Z axis. For example, in the miniaturized flap maker system of <FIG>, this can be done by coordinating the XY scanner <NUM>, and the Fast-Z scanner <NUM> via the software, e.g., via the controller <NUM>. The procedure starts with the scan line being parallel to the XY plane, and sweeps through the apex of the lens, following the curvature with the largest diameter (see also FIG. Multiple sweeps are performed at successive angular directions with respect to the Z axis, for example as realized by rotating the prism <NUM> because successive sweeps, to form the entire lenticule. With this preferred procedure, there are no vertical "steps" in the dissection, and vertical side cuts are eliminated. As will be analyzed herein below, the deviations between the laser focus locations and the intended spherical surface dissections are also minimized.

<FIG> shows the geometric relation between the fast scan line <NUM> and the intended spherical dissection surface <NUM>, e.g., of a lens, especially the distance deviation (δ) between the end point B of the scan line <NUM> and point A on the intended dissection surface <NUM>. The maximum deviation δ is the distance between point A and point B, and is given by (Equation (<NUM>)): <MAT> where R is greater than L. R is the radius of curvature of the surface dissection <NUM>, and L is the length of the fast scan.

While the above maximum deviation analysis is for a spherical surface, this scanning method may also be used to create a smooth cut having a non-spherical shape , such as an ellipsoidal shape, etc. In such a case, the parallel of latitude and/or the meridian of longitude may not be circular.

In an exemplary case of myopic correction, the radius of curvature of the surface dissection may be determined by the amount of correction, ΔD, using the following equation (Equation (<NUM>)): <MAT> where n=<NUM>, which is the refractive index of cornea, and R<NUM> and R<NUM> (may also be referred herein as Rt and Rb) are the radii of curvature for the top surface and bottom surface of a lenticular incision, respectively. For a lenticular incision with R<NUM>=R<NUM>=R (the two dissection surface are equal for them to physically match and be in contact), we have (Equation (<NUM>)): <MAT>.

<FIG> is a top view <NUM> of a lenticular incision <NUM> which illustrates three exemplary sweeps (1A to 1B), (2A to 2B) and (3A to 3B), with each sweep going through (i.e., going over) the lenticular incision apex <NUM>. The incision diameter <NUM> (DCUT) should be equal to or greater than the to-be-extracted lenticular incision diameter <NUM> (DL). A top view <NUM> shows the top view of one exemplary sweep.

Using such a "fast-scan-slow-sweep" scanning scheme, each sweep of the fast scan line forms a bent band, the bent band being the equivalent of bending a flat rectangle such that its long sides form arched shapes (the shape of the meridian of longitude) while its short sides remain straight. In the top view in <FIG> and <FIG>, the rectangular shapes represent the sweeps. In the central area of the lenticule cut, i.e. the area closer to the apex, multiple sweeps overlap each other. The amount of overlap decreases toward the edge of the lenticule cut. The inventors recognized that when the sweeping speed of each sweeps is constant, the central area experiences significant redundant cutting, causing unnecessary high energy deposit in this area. This is disadvantages because it may cause unnecessary cavitation bubbles which in turn may cause light scattering induced glare and halo. In particular, the high energy area is located at the center of the visual field, making it even more undesirable. Thus, the present invention may alleviate this problem by speeding up the sweep in the central area of the lenticule. Moreover, speeding up the sweep in the central area will reduce the total amount of time require for producing the lenticule incisions.

Therefore, the sweeping speed of each sweep is controlled to vary along the sweeping path (the meridian of longitude), with the speed being the highest in the areas near the apex (the midpoint of each sweep) where all sweeps overlap, and the lowest at the edge of the lenticule (the start and end portions of each sweep) where multiple sweeps have substantially no overlap, as schematically shown in <FIG> (side view) and 8B (top view). The sweeping speed in the portions between the midpoint and the end points varies between the lowest and the highest speeds. The sweeping speed may vary in a continuous manner or in a stepwise manner.

Preferably, the lowest sweeping speed is determined by the required spatial density of the laser focal spots that is sufficient to form an incision surface that will result in tissue-bridge free separation of the tissue, such that a single sweep (i.e. no overlap with other sweeps) at the lowest sweeping speed will produce the required focal point density. The upper limit of the highest sweeping speed may be determined by the degree of overlap in the central area of the lenticule. If the scan pattern includes a total of N sweeps at different angles to form the entire lenticule, then in the central area having a diameter approximately equal to the width of the sweep, the upper limit of the highest sweeping speed may be N times the lowest speed, as all N sweeps will overlap in that area. In practice, the highest speed at the midpoint does not need to reach this upper speed limit, and a significant time reduction can still be achieved.

The sweeping speed may be controlled according to the following equation (Equation (<NUM>)): <MAT> where r is the radial position (i.e. the distance from the Z axis) of the fast scan line; R is the lateral radius of the lenticule; V(r) is the radial velocity (the sweeping speed) of the fast scan line as a function of the radial position r; Vmax is the maximum velocity (the highest sweeping speed) at the center of the lenticule, and Vmin is the minimum velocity (the lowest sweeping speed) at the edge of the lenticule.

Equation (<NUM>) is only an example; other suitable function for V(r) may be used. More generally, the variable sweeping speed is a first speed at the apex and a second speed at the edges, the first speed being higher than the second speed.

Using a variable sweeping speed, the total lenticule cutting time may be reduced by <NUM>% or more as compared to using a constant sweeping speed equal to the lowest speed. In one example, using a variable sweeping speed according to the above Equation (<NUM>), with the lowest speed Vmin being <NUM>/s and the highest speed Vmax being <NUM>/s, the total cutting time was approximately <NUM> seconds. The laser pulse frequency was <NUM> and the fast scan frequency of the resonant scanner was <NUM>. In comparison, using a constant sweeping speed of <NUM>/s, with other parameters being equal, the total cutting time was approximately <NUM> seconds. Both cases achieved tissue-bridge free lenticule extraction. <FIG> shows a comparison of the cutting pattern (top view) for the constant speed sweeps (left) and variable speed sweeps (right). The laser spot density in the central area was significantly reduced.

The scanning method using variable sweeping speed allows optimizing the sweeping speed while keeping a substantially uniform distribution of laser focal spots across the lenticule surface, facilitating easy lenticule extraction.

The lenticular incision may be performed in the following steps:.

For illustrative purposes, in a myopic correction of ΔD=<NUM> diopter (i.e., <NUM>/m), using equation (<NUM>), R=<NUM>, which is indeed much greater than the length L of the fast scan. Assuming a reasonable scan line length of L=<NUM>, using equation (<NUM>), the deviation δ=<NUM>. This deviation is thus very small. For comparison purpose, the depth of focus of a one micron (FWHM) spot size at <NUM> wavelength is about ±<NUM>, meaning the length of focus is greater than the deviation δ.

<FIG> illustrates a process of the laser system <NUM>. The laser system <NUM> may start a surgical procedure performing pre-operation measurements (Action Block <NUM>). For example, in an ophthalmologic surgery for myopic correction, the myopic diopter is determined, the reference depth position is determined, and so on. The laser system <NUM> calculates the radius of curvature based on the amount of correction, e.g., the myopic correction determined in pre-operation measurements, as shown, for example, in equations (<NUM>) and (<NUM>) above, and calculates the diameter of the incision, as shown by DCUT in <FIG> (Action Block <NUM>). DCUT is equal to or greater than the diameter of the to-be-extracted lenticule (DL in <FIG>). The system select various laser and optical system parameters, including the sweeping speed as a function of radial position V(r) along with the parameters Vmin and Vmax (Action Block <NUM>).

The laser system <NUM> first performs side incision to provide a vent for gas that can be produced in the lenticular surface dissections, and for tissue extraction later on (Action Block <NUM>). The laser system <NUM> then performs the bottom lenticular surface dissection (Action Block <NUM>) before performing the top lenticular surface dissection (Action Block <NUM>). The bottom and top lenticular surface dissection are performed using a fast-scan-slow-sweep scheme along the meridians of longitude, with variably sweeping speed, as described above. The lenticular tissue is then extracted (Action Block <NUM>).

The variable sweeping speed method has many advantages over the conventional constant sweeping speed method. It avoids redundant cutting, which reduces unnecessary cavitation bubbles, particularly at the center of the visual field, and thus reduces light scattering-induced glare and halo in the patient's eye. It reduces the time of the lenticular incision procedure (e.g. by <NUM>%) without compromising the tissue-bridge free incision quality. Advantages of reduced procedure time includes: reduced patient discomfort during eye docking (docking refers to physically coupling the patient's eye to the laser system optics using a patient interface device); reduced risk of incision failure due to insecure coupling of the patient interface device to the eye (for example, when a patient interface uses suction force to couple the patient interface to the eye surface, suction loss may cause failure of the coupling); reduced risk of damage to the sclera due to long applanation (the flattening of the corneal by the patient interface device) and suction; and reduced risk of damage to retina due to high intraocular pressure during docking.

The above described laser energy systems solve the problem of redundant energy deposit near the central area by increasing the sweeping speed near the central area. In alternative laser energy systems, this problem may be solved by varying other parameters of the laser system, including: controlling the laser device to dynamically reduce the laser pulse energy when the scan line is located in a central area of the lenticule (e.g. an area having a diameter approximately equal to the width of the sweep) during the sweep as compared to when the scan line is located near the edge of the lenticule; increasing the width of the fast scan line, without changing the number of pulses per scan line (that is a function of the laser), so that the energy density (total energy per area) is reduced. All of these methods reduce the energy density near the center of the field of view.

The use of the terms "a" and "an" and "the" and similar referents in the context of describing the invention (especially in the context of the following claims) are to be construed to cover both the singular and the plural, unless otherwise indicated herein or clearly contradicted by context. The term "connected" is to be construed as partly or wholly contained within, attached to, or joined together, even if there is something intervening. All methods described herein do not form part of the claimed invention, but provide explanatory context to the system as claimed. Said methods can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context. The use of any and all examples, or exemplary language (e.g., "such as") provided herein, is intended merely to better illuminate embodiments of the invention and does not pose a limitation on the scope of the invention unless otherwise claimed.

Claim 1:
An ophthalmic surgical laser system comprising:
a laser (<NUM>) for generating a pulsed laser beam;
a laser delivery system for delivering a pulsed laser beam to a target in a subject's eye;
a high frequency scanner to scan the pulsed laser beam back and forth at a predefined frequency;
an XY-scanner (<NUM>) to deflect the pulsed laser beam, the XY-scanner being separate from the high frequency scanner;
a Z-scanner (<NUM>) to modify a depth of a focus of the pulsed laser beam; and
a controller (<NUM>) configured to control the high frequency scanner, the XY-scanner (<NUM>) and the Z-scanner (<NUM>) to successively form a plurality of sweeps which collectively form at least one lenticular incision of a lens in the subject's eye, the lens having a curved surface that defines an apex and a Z axis passing through the apex, wherein each sweep is formed by:
controlling the high frequency scanner to deflect the pulsed laser beam to form a scan line, the scan line being a straight line having a predefined length and being tangential to a parallel of latitude of the lens, the parallel of latitude being a circle on the surface of the lens that is perpendicular to the Z axis and has a defined distance to the apex, and
controlling the XY-scanner (<NUM>) and the Z-scanner (<NUM>) to move the scan line along a meridian of longitude of the lens, the meridian of longitude being a curve that passes through the apex and has a defined angular position around the Z axis, wherein a sweeping speed of moving the scan line along the meridian of longitude varies with a position of the scan line along the meridian of longitude, wherein the sweeping speed is higher when the scan line passes through the apex than when the scan line is at an edge of the lenticular incision,
wherein the plurality of sweeps are successively formed one after another along the respective meridians of longitude which are different from one another.