the present invention can be implemented by a system that projects or scans an optical beam into a patient &# 39 ; s eye 1 , such as the system shown in fig1 . the system includes a light source 10 ( e . g . laser , laser diode , etc . ), which may be controlled by control electronics 12 , via an input and output device 14 , to create optical beam 11 ( either cw or pulsed ). control electronics 12 may be a computer , microcontroller , etc . scanning may be achieved by using one or more moveable optical elements ( e . g . lenses , gratings , or as shown in fig1 a mirror ( s ) 16 ) which also may be controlled by control electronics 12 , via input and output device 14 . mirror 16 may be tilted to deviate the optical beam 11 as shown in fig1 , and direct beam 11 towards the patient &# 39 ; s eye 1 . an optional ophthalmic lens 18 can be used to focus the optical beam 11 into the patient &# 39 ; s eye 1 . the positioning and character of optical beam 11 and / or the scan pattern it forms on the eye may be further controlled by use of an input device 20 such as a joystick , or any other appropriate user input device . techniques herein include utilizing a light source 10 such as a surgical laser configured to provide one or more of the following parameters : 1 ) pulse energy up to 1 μj repetition rate up to 1 mhz , pulse duration & lt ; 1 ps 2 ) pulse energy up to 10 μj rep . rate up to 100 khz , pulse duration & lt ; 1 ps . 3 ) pulse energy up to 1000 μj , rep rate up to 1 khz , pulse duration & lt ; 3 ps . additionally , the laser may use wavelengths in a variety of ranges including in the near - infrared range : 800 - 1100 nm . in one aspect , near - infrared wavelengths are selected because tissue absorption and scattering is reduced . additionally , a laser can be configured to provide low energy ultrashort pulses of near - infrared radiation with pulse durations below 10 ps or below 1 ps , alone or in combination with pulse energy not exceeding 100 μj , at high repetition rate including rates above 1 khz , and above 10 khz . short pulsed laser light focused into eye tissue 2 will produce dielectric breakdown at the focal point , rupturing the tissue 2 in the vicinity of the photo - induced plasma ( see fig2 ). the diameter d of the focal point is given by d = λf / d b , where f is the focal length of the last focusing element , d b is the beam diameter on the last lens , and λ is the wavelength . for a focal length f = 160 mm , beam diameter on the last lens d b = 10 mm , and wavelength λ = 1 . 04 um , the focal spot diameter will be d ≈ λ /( 2 . na )≈ λf / d b = 15 where the numerical aperture of the focusing optics , na ≈ d b /( 2f ). to provide for continuous cutting , the laser spots should not be separated by more than a width of the crater produced by the laser pulse in tissue . assuming the rupture zone being r = 15 μm ( at low energies ionization might occur in the center of the laser spot and not expand to the full spot size ), and assuming the maximal diameter of the capsulotomy circle being d c = 8 mm , the number of required pulses will be : n = πd c / r = 1675 to provide a circular cut line 22 around the circumference of the eye lens 3 as illustrated in fig3 . for smaller diameters ranging from 5 - 7 mm , the required number of pulses would be less . if the rupture zone were larger ( e . g . 50 μm ), the number of pulses would drop to n = 503 . to produce an accurate circular cut , these pulses should be delivered to tissue over a short eye fixation time . assuming the fixation time t = 0 . 2 s , laser repetition rate should be : r = n / t = 8 . 4 khz . if the fixation time were longer , e . g . 0 . 5 s , the required rep . rate could be reduced to 3 . 4 khz . with a rupture zone of 50 μm the rep . rate could further drop to 1 khz . threshold radiant exposure of the dielectric breakdown with 4 ns pulses is about φ = 100 j / cm 2 . with a focal spot diameter being d = 15 μm , the threshold pulse energy will be e th = φ * πd 2 / 4 = 176 μj . for stable and reproducible operation , pulse energy should exceed the threshold by at least a factor of 2 , so pulse energy of the target should be e = 352 μj . the creation of a cavitation bubble might take up to 10 % of the pulse energy , i . e . e b = 35 μj . this corresponds to a bubble diameter the energy level can be adjusted to avoid damage to the corneal endothelium . as such , the threshold energy of the dielectric breakdown could be minimized by reducing the pulse duration , for example , in the range of approximately 0 . 1 - 1 ps . threshold radiant exposure , φ , for dielectric breakdown for 100 fs is about φ = 2 j / cm 2 ; for 1 ps it is φ = 2 . 5 j / cm 2 . using the above pulse durations , and a focal spot diameter d = 15 μm , the threshold pulse energies will be e th = φ * πd 2 / 4 = 3 . 5 and 4 . 4 μj for 100 fs and 1 ps pulses , respectively . the pulse energy could instead be selected to be a multiple of the threshold energy , for example , at least a factor of 2 . if a factor of 2 is used , the pulse energies on the target would be e th = 7 and 9 μj , respectively . these are only two examples . other pulse energy duration times , focal spot sizes and threshold energy levels are possible and are within the scope of the present invention . a high repetition rate and low pulse energy can be utilized for tighter focusing of the laser beam . in one specific example , a focal distance of f = 50 mm is used while the beam diameter remains d b = 10 mm , to provide focusing into a spot of about 4 μm in diameter . aspherical optics can also be utilized . an 8 mm diameter opening can be completed in a time of 0 . 2 s using a repetition rate of about 32 khz . the laser 10 and controller 12 can be set to locate the surface of the capsule and ensure that the beam will be focused on the lens capsule at all points of the desired opening . imaging modalities and techniques described herein , such as for example , optical coherence tomography ( oct ) or ultrasound , may be used to determine the location and measure the thickness of the lens and lens capsule to provide greater precision to the laser focusing methods , including 2d and 3d patterning . laser focusing may also be accomplished using one or more methods including direct observation of an aiming beam , optical coherence tomography ( oct ), ultrasound , or other known ophthalmic or medical imaging modalities and combinations thereof . as shown in fig4 , oct imaging of the anterior chamber can be performed along a simple linear scan 24 across the lens using the same laser and / or the same scanner used to produce the patterns for cutting . this scan will provide information about the axial location of the anterior and posterior lens capsule , the boundaries of the cataract nucleus , as well as the depth of the anterior chamber . this information may then be loaded into the laser 3 - d scanning system , and used to program and control the subsequent laser assisted surgical procedure . the information may be used to determine a wide variety of parameters related to the procedure such as , for example , the upper and lower axial limits of the focal planes for cutting the lens capsule and segmentation of the lens cortex and nucleus , the thickness of the lens capsule among others . the imaging data may be averaged across a 3 - line pattern as shown in fig9 . an example of the results of such a system on an actual human crystalline lens is shown in fig2 . a beam of 10 μj , 1 ps pulses delivered at a pulse repetition rate of 50 khz from a laser operating at a wavelength of 1045 nm was focused at na = 0 . 05 and scanned from the bottom up in a pattern of 4 circles in 8 axial steps . this produced the fragmentation pattern in the ocular lens shown in fig2 . fig2 shows in detail the resultant circular incisions , which measured ˜ 10 μm in diameter , and ˜ 100 μm in length . fig2 illustrates an exemplary illustration of the delineation available using the techniques described herein to anatomically define the lens . as can be seen in fig2 , the capsule boundaries and thickness , the cortex , epinucleus and nucleus are determinable . it is believed that oct imaging may be used to define the boundaries of the nucleus , cortex and other structures in the lens including , for example , the thickness of the lens capsule including all or a portion of the anterior or posterior capsule . in the most general sense , one aspect of the present invention is the use of ocular imaging data obtained as described herein as an input into a laser scanning and / or pattern treatment algorithm or technique that is used to as a guide in the application of laser energy in novel laser assisted ophthalmic procedures . in fact , the imaging and treatment can be performed using the same laser and the same scanner . while described for use with lasers , other energy modalities may also be utilized . it is to be appreciated that plasma formation occurs at the waist of the beam . the axial extent of the cutting zone is determined by the half - length l of the laser beam waist , which can be expressed as : l ˜ λ /( 4 . na 2 )= df / d b . thus the lower the na of the focusing optics , the longer waist of the focused beam , and thus a longer fragmentation zone can be produced . for f = 160 mm , beam diameter on the last lens d b = 10 mm , and focal spot diameter d = 15 the laser beam waist half - length l would be 240 μm . with reference to fig5 , a three dimensional application of laser energy 26 can be applied across the capsule along the pattern produced by the laser - induced dielectric breakdown in a number of ways such as , for example : 1 ) producing several circular or other pattern scans consecutively at different depths with a step equal to the axial length of the rupture zone . thus , the depth of the focal point ( waist ) in the tissue is stepped up or down with each consecutive scan . the laser pulses are sequentially applied to the same lateral pattern at different depths of tissue using , for example , axial scanning of the focusing elements or adjusting the optical power of the focusing element while , optionally , simultaneously or sequentially scanning the lateral pattern . the adverse result of laser beam scattering on bubbles , cracks and / or tissue fragments prior to reaching the focal point can be avoided by first producing the pattern / focusing on the maximal required depth in tissue and then , in later passes , focusing on more shallow tissue spaces . not only does this “ bottom up ” treatment technique reduce unwanted beam attenuation in tissue above the target tissue layer , but it also helps protect tissue underneath the target tissue layer . by scattering the laser radiation transmitted beyond the focal point on gas bubbles , cracks and / or tissue fragments which were produced by the previous scans , these defects help protect the underlying retina . similarly , when segmenting a lens , the laser can be focused on the most posterior portion of the lens and then moved more anteriorly as the procedure continues . a ) using a sequence of 2 - 3 pulses in each spot separated by a few ps . each pulse will be absorbed by the plasma 28 produced by the previous pulse and thus will extend the plasma 28 upwards along the beam as illustrated in fig6 a . in this approach , the laser energy should be 2 or 3 times higher , i . e . 20 - 30 μj . delay between the consecutive pulses should be longer than the plasma formation time ( on the order of 0 . 1 ps ) but not exceed the plasma recombination time ( on the order of nanoseconds ) b ) producing an axial sequence of pulses with slightly different focusing points using multiple co - axial beams with different pre - focusing or multifocal optical elements . this can be achieved by using multi - focal optical elements ( lenses , mirrors , diffractive optics , etc .). for example , a multi - segmented lens 30 can be used to focus the beam into multiple points ( e . g . three separate points ) along the same axis , using for example co - axial ( see fig7 a - 7c ) or off - coaxial ( see fig7 d ) segments to produce varying focal lengths ( e . g . f 1 , f 2 , f 3 ). the multi - focal element 30 can be co - axial , or off - axis - segmented , or diffractive . co - axial elements may have more axially - symmetric focal points , but will have different sizes due to the differences in beam diameters in each segment . off - axial elements might have less symmetric focal points but all the elements can produce the foci of the same sizes . c ) producing an elongated focusing column ( as opposed to just a discrete number of focal points ) using : ( 1 ) non - spherical ( aspherical ) optics , or ( 2 ) utilizing spherical aberrations in a lens with a high f number , or ( 3 ) diffractive optical element ( hologram ). d ) producing an elongated zone of ionization using multiple optical fibers . for example , an array of optical fibers 32 of different lengths can be imaged with a set of lenses 34 into multiple focal points at different depths inside the tissue as shown in fig8 . for anterior and posterior capsulotomy , the scanning patterns can be circular and spiral , with a vertical step similar to the length of the rupture zone . for segmentation of the eye lens 3 , the patterns can be linear , planar , radial , radial segments , circular , spiral , curvilinear and combinations thereof including patterning in two and / or three dimensions . scans can be continuous straight or curved lines , or one or more overlapping or spaced apart spots and / or line segments . several scan patterns 36 are illustrated in fig9 a and 9b , and combinations of scan patterns 38 are illustrated in fig1 a - 10c . beam scanning with the multifocal focusing and / or patterning systems is particularly advantageous to successful lens segmentation since the lens thickness is much larger than the length of the beam waist axial . in addition , these and other 2d and 3d patterns may be used in combination with oct to obtain additional imaging , anatomical structure or make - up ( i . e ., tissue density ) or other dimensional information about the eye including but not limited to the lens , the cornea , the retina and as well as other portions of the eye . the exemplary patterns allow for dissection of the lens cortex and nucleus into fragments of such dimensions that they can be removed simply with an aspiration needle , and can be used alone to perform capsulotomy . alternatively , the laser patterning may be used to pre - fragment or segment the nucleus for later conventional ultrasonic phacoemulsification . in this case however , the conventional phacoemulsification would be less than a typical phacoemulsification performed in the absence of the inventive segmenting techniques because the lens has been segmented . as such , the phacoemulsification procedure would likely require less ultrasonic energy to be applied to the eye , allowing for a shortened procedure or requiring less surgical dexterity . complications due to the eye movements during surgery can be reduced or eliminated by performing the patterned laser cutting very rapidly ( e . g . within a time period that is less than the natural eye fixation time ). depending on the laser power and repetition rate , the patterned cutting can be completed between 5 and 0 . 5 seconds ( or even less ), using a laser repetition rate exceeding 1 khz . the techniques described herein may be used to perform new ophthalmic procedures or improve existing procedures , including anterior and posterior capsulotomy , lens fragmentation and softening , dissection of tissue in the posterior pole ( floaters , membranes , retina ), as well as incisions in other areas of the eye such as , but not limited to , the sclera and iris . damage to an iol during posterior capsulotomy can be reduced or minimized by advantageously utilizing a laser pattern initially focused beyond the posterior pole and then gradually moved anteriorly under visual control by the surgeon alone or in combination with imaging data acquired using the techniques described herein . for proper alignment of the treatment beam pattern , an alignment beam and / or pattern can be first projected onto the target tissue with visible light ( indicating where the treatment pattern will be projected . this allows the surgeon to adjust the size , location and shape of the treatment pattern . thereafter , the treatment pattern can be rapidly applied to the target tissue using an automated 3 dimensional pattern generator ( in the control electronics 12 ) by a short pulsed cutting laser having high repetition rate . in addition , and in particular for capsulotomy and nuclear fragmentation , an automated method employing an imaging modality can be used , such as for example , electro - optical , oct , acoustic , ultrasound or other measurement , to first ascertain the maximum and minimum depths of cutting as well as the size and optical density of the cataract nucleus . such techniques allow the surgeon account for individual differences in lens thickness and hardness , and help determine the optimal cutting contours in patients . the system for measuring dimensions of the anterior chamber using oct along a line , and / or pattern ( 2d or 3d or others as described herein ) can be integrally the same as the scanning system used to control the laser during the procedure . as such , the data including , for example , the upper and lower boundaries of cutting , as well as the size and location of the nucleus , can be loaded into the scanning system to automatically determine the parameters of the cutting ( i . e ., segmenting or fracturing ) pattern . additionally , automatic measurement ( using an optical , electro - optical , acoustic , or oct device , or some combination of the above ) of the absolute and relative positions and / or dimensions of a structure in the eye ( e . g . the anterior and posterior lens capsules , intervening nucleus and lens cortex ) for precise cutting , segmenting or fracturing only the desired tissues ( e . g . lens nucleus , tissue containing cataracts , etc .) while minimizing or avoiding damage to the surrounding tissue can be made for current and / or future surgical procedures . additionally , the same ultrashort pulsed laser can be used for imaging at a low pulse energy , and then for surgery at a high pulse energy . the use of an imaging device to guide the treatment beam may be achieved many ways , such as those mentioned above as well as additional examples explained next ( which all function to characterize tissue , and continue processing it until a target is removed ). for example , in fig1 , a laser source ls and ( optional ) aiming beam source aim have outputs that are combined using mirror dm 1 ( e . g . dichroic mirror ). in this configuration , laser source ls may be used for both therapeutics and diagnostics . this is accomplished by means of mirror m 1 which serves to provide both reference input r and sample input s to an oct interferometer by splitting the light beam b ( centerlines shown ) from laser source ls . because of the inherent sensitivity of oct interferometers , mirror m 1 may be made to reflect only a small portion of the delivered light . alternatively , a scheme employing polarization sensitive pickoff mirrors may be used in conjunction with a quarter wave plate ( not shown ) to increase the overall optical efficiency of the system . lens l 1 may be a single element or a group of elements used to adjust the ultimate size or location along the z - axis of the beam b disposed to the target at point p . when used in conjunction with scanning in the x & amp ; y axes , this configuration enables 3 - dimensional scanning and / or variable spot diameters ( i . e . by moving the focal point of the light along the z - axis ). in this example , transverse ( xy ) scanning is achieved by using a pair of orthogonal galvanometric mirrors g 1 & amp ; g 2 which may provide 2 - dimensional random access scanning of the target . it should be noted that scanning may be achieved in a variety of ways , such as moving mirror m 2 , spinning polygons , translating lenses or curved mirrors , spinning wedges , etc . and that the use of galvanometric scanners does not limit the scope of the overall design . after leaving the scanner , light encounters lens l 2 which serves to focus the light onto the target at point p inside the patient &# 39 ; s eye eye . an optional ophthalmic lens ol may be used to help focus the light . ophthalmic lens ol may be a contact lens and further serve to dampen any motion of eye eye , allowing for more stable treatment . lens l 2 may be made to move along the z - axis in coordination with the rest of the optical system to provide for 3 - dimensional scanning , both for therapy and diagnosis . in the configuration shown , lens l 2 ideally is moved along with the scanner g 1 & amp ; g 2 to maintain telecentricity . with that in mind , one may move the entire optical assembly to adjust the depth along the z - axis . if used with ophthalmic lens ol , the working distance may be precisely held . a device such as the thorlabs eas504 precision stepper motor can be used to provide both the length of travel as well as the requisite accuracy and precision to reliably image and treat at clinically meaningful resolutions . as shown it creates a telecentric scan , but need not be limited to such a design . mirror m 2 serves to direct the light onto the target , and may be used in a variety of ways . mirror m 2 could be a dichroic element that the user looks through in order to visualize the target directly or using a camera , or may be made as small as possible to provide an opportunity for the user to view around it , perhaps with a binocular microscope . if a dichroic element is used , it may be made to be photopically neutral to avoid hindering the user &# 39 ; s view . an apparatus for visualizing the target tissue is shown schematically as element v , and is preferably a camera with an optional light source for creating an image of the target tissue . the optional aiming beam aim may then provide the user with a view of the disposition of the treatment beam , or the location of the identified targets . to display the target only , aim may be pulsed on when the scanner has positioned it over an area deemed to be a target . the output of visualization apparatus v may be brought back to the system via the input / output device io and displayed on a screen , such as a graphical user interface gui . in this example , the entire system is controlled by the controller cpu , and data moved through input / output device io . graphical user interface gui may be used to process user input , and display the images gathered by both visualization apparatus v and the oct interferometer . there are many possibilities for the configuration of the oct interferometer , including time and frequency domain approaches , single and dual beam methods , etc , as described in u . s . pat . nos . 5 , 748 , 898 ; 5 , 748 , 352 ; 5 , 459 , 570 ; 6 , 111 , 645 ; and 6 , 053 , 613 ( which are incorporated herein by reference . information about the lateral and axial extent of the cataract and localization of the boundaries of the lens capsule will then be used for determination of the optimal scanning pattern , focusing scheme , and laser parameters for the fragmentation procedure . much if not all of this information can be obtained from visualization of the target tissue . for example , the axial extent of the fragmentation zone of a single pulse should not exceed the distance between ( a ) the cataract and the posterior capsule , and ( b ) the anterior capsule and the corneal endothelium . in the cases of a shallow anterior chamber and / or a large cataract , a shorter fragmentation zone should be selected , and thus more scanning planes will be required . conversely , for a deep anterior chamber and / or a larger separation between the cataract and the posterior capsule a longer fragmentation zone can be used , and thus less planes of scanning will be required . for this purpose an appropriate focusing element will be selected from an available set . selection of the optical element will determine the width of the fragmentation zone , which in turn will determine the spacing between the consecutive pulses . this , in turn , will determine the ratio between the scanning rate and repetition rate of the laser pulses . in addition , the shape of the cataract will determine the boundaries of the fragmentation zone and thus the optimal pattern of the scanner including the axial and lateral extent of the fragmentation zone , the ultimate shape of the scan , number of planes of scanning , etc . fig1 shows an alternate embodiment in which the imaging and treatment sources are different . a dichroic mirror dm 2 has been added to the configuration of fig1 to combine the imaging and treatment light , and mirror m 1 has been replaced by beam splitter bs which is highly transmissive at the treatment wavelength , but efficiently separates the light from the imaging source sld for use in the oct interferometer . imaging source sld may be a superluminescent diode having a spectral output that is nominally 50 nm wide , and centered on or around 835 nm , such as the superlum sld - 37 . such a light source is well matched to the clinical application , and sufficiently spectrally distinct from the treatment source , thus allowing for elements dm and bs to be reliably fabricated without the necessarily complicated and expensive optical coatings that would be required if the imaging and treatment sources were closer in wavelength . fig1 shows an alternate embodiment incorporating a confocal microscope cm for use as an imaging system . in this configuration , mirror m 1 reflects a portion of the backscattered light from beam b into lens l 3 . lens l 3 serves to focus this light through aperture a ( serving as a spatial filter ) and ultimately onto detector d . as such , aperture a and point p are optically conjugate , and the signal received by detector d is quite specific when aperture a is made small enough to reject substantially the entire background signal . this signal may thus be used for imaging , as is known in the art . furthermore , a fluorophore may be introduced into the target to allow for specific marking of either target or healthy tissue . in this approach , the ultrafast laser may be used to pump the absorption band of the fluorophore via a multiphoton process or an alternate source ( not shown ) could be used in a manner similar to that of fig1 . fig1 is a flowchart outlining the steps utilized in a “ track and treat ” approach to material removal . first an image is created by scanning from point to point , and potential targets identified . when the treatment beam is disposed over a target , the system can transmit the treatment beam , and begin therapy . the system may move constantly treating as it goes , or dwell in a specific location until the target is fully treated before moving to the next point . the system operation of fig1 could be modified to incorporate user input . as shown in fig1 , a complete image is displayed to the user , allowing them to identify the target ( s ). once identified , the system can register subsequent images , thus tracking the user defined target ( s ). such a registration scheme may be implemented in many different ways , such as by use of the well known and computationally efficient sobel or canny edge detection schemes . alternatively , one or more readily discernable marks may be made in the target tissue using the treatment laser to create a fiduciary reference without patient risk ( since the target tissue is destined for removal ). in contrast to conventional laser techniques , the above techniques provide ( a ) application of laser energy in a pattern , ( b ) a high repetition rate so as to complete the pattern within the natural eye fixation time , ( c ) application of sub - ps pulses to reduce the threshold energy , and ( d ) the ability to integrate imaging and treatment for an automated procedure . the laser delivery system in fig1 can be varied in several ways . for example , the laser source could be provided onto a surgical microscope , and the microscope &# 39 ; s optics used by the surgeon to apply the laser light , perhaps through the use of a provided console . alternately , the laser and delivery system would be separate from the surgical microscope and would have an optical system for aligning the aiming beam for cutting . such a system could swing into position using an articulating arm attached to a console containing the laser at the beginning of the surgery , and then swing away allowing the surgical microscope to swing into position . the pattern to be applied can be selected from a collection of patterns in the control electronics 12 , produced by the visible aiming beam , then aligned by the surgeon onto the target tissue , and the pattern parameters ( including for example , size , number of planar or axial elements , etc .) adjusted as necessary for the size of the surgical field of the particular patient ( level of pupil dilation , size of the eye , etc .). thereafter , the system calculates the number of pulses that should be applied based on the size of the pattern . when the pattern calculations are complete , the laser treatment may be initiated by the user ( i . e ., press a pedal ) for a rapid application of the pattern with a surgical laser . the laser system can automatically calculate the number of pulses required for producing a certain pattern based on the actual lateral size of the pattern selected by surgeon . this can be performed with the understanding that the rupture zone by the single pulse is fixed ( determined by the pulse energy and configuration of the focusing optics ), so the number of pulses required for cutting a certain segment is determined as the length of that segment divided by the width of the rupture zone by each pulse . the scanning rate can be linked to the repetition rate of the laser to provide a pulse spacing on tissue determined by the desired distance . the axial step of the scanning pattern will be determined by the length of the rupture zone , which is set by the pulse energy and the configuration of the focusing optics . the methods and systems described herein can be used alone or in combination with an aplanatic lens ( as described in , for example , the u . s . pat . no . 6 , 254 , 595 patent , incorporated herein by reference ) or other device to configure the shape of the cornea to assist in the laser methods described herein . a ring , forceps or other securing means may be used to fixate the eye when the procedure exceeds the normal fixation time of the eye . regardless whether an eye fixation device is used , patterning and segmenting methods described herein may be further subdivided into periods of a duration that may be performed within the natural eye fixation time . another potential complication associated with a dense cutting pattern of the lens cortex is the duration of treatment : if a volume of 6 × 6 × 4 mm = 144 mm 3 of lens is segmented , it will require n = 722 , 000 pulses . if delivered at 50 khz , it will take 15 seconds , and if delivered at 10 khz it will take 72 seconds . this is much longer than the natural eye fixation time , and it might require some fixation means for the eye . thus , only the hardened nucleus may be chosen to be segmented to ease its removal . determination of its boundaries with the oct diagnostics will help to minimize the size of the segmented zone and thus the number of pulses , the level of cumulative heating , and the treatment time . if the segmentation component of the procedure duration exceeds the natural fixation time , then the eye may be stabilized using a conventional eye fixation device . in cases where very dense patterns of cutting are needed or desired , excess accumulation of heat in the lens may damage the surrounding tissue . to estimate the maximal heating , assume that the bulk of the lens is cut into cubic pieces of 1 mm in size . if tissue is dissected with e 1 = 10 uj pulses fragmenting a volume of 15 um in diameter and 200 um in length per pulse , then pulses will be applied each 15 um . thus a 1 × 1 mm plane will require 66 × 66 = 4356 pulses . the 2 side walls will require 2 × 66 × 5 = 660 pulses , thus total n = 5016 pulses will be required per cubic mm of tissue . since all the laser energy deposited during cutting will eventually be transformed into heat , the temperature elevation will be dt =( e 1 * n )/ pcv = 50 . 16 mj /( 4 . 19 mj / k )= 12 k . this will lead to maximal temperature t = 37 + 12 ° c .= 49 ° c . this heat will dissipate in about one minute due to heat diffusion . since peripheral areas of the lens will not be segmented ( to avoid damage to the lens capsule ) the average temperature at the boundaries of the lens will actually be lower . for example , if only half of the lens volume is fragmented , the average temperature elevation at the boundaries of the lens will not exceed 6 ° c . ( t = 43 ° c .) and on the retina will not exceed 0 . 1 c . such temperature elevation can be well tolerated by the cells and tissues . however , much higher temperatures might be dangerous and should be avoided . to reduce heating , a pattern of the same width but larger axial length can be formed , so these pieces can still be removed by suction through a needle . for example , if the lens is cut into pieces of 1 × 1 × 4 mm in size , a total of n = 6996 pulses will be required per 4 cubic mm of tissue . the temperature elevation will be dt =( e 1 * n )/ pcv = 69 . 96 mj /( 4 . 19 mj / k )/ 4 = 1 . 04 k . such temperature elevation can be well tolerated by the cells and tissues . an alternative solution to thermal limitations can be the reduction of the total energy required for segmentation by tighter focusing of the laser beam . in this regime a higher repetition rate and low pulse energy may be used . for example , a focal distance of f = 50 mm and a beam diameter of d b = 10 mm would allow for focusing into a spot of about 4 μm in diameter . in this specific example , repetition rate of about 32 khz provides an 8 mm diameter circle in about 0 . 2 s . to avoid retinal damage due to explosive vaporization of melanosomes following absorption of the short laser pulse the laser radiant exposure on the rpe should not exceed 100 mj / cm 2 . thus na of the focusing optics should be adjusted such that laser radiant exposure on the retina will not exceed this safety limit . with a pulse energy of 10 μj , the spot size on retina should be larger than 0 . 1 mm in diameter , and with a 1 mj pulse it should not be smaller than 1 mm . assuming a distance of 20 mm between lens and retina , these values correspond to minimum numerical apertures of 0 . 0025 and 0 . 025 , respectively . to avoid thermal damage to the retina due to heat accumulation during the lens fragmentation the laser irradiance on the retina should not exceed the thermal safety limit for near - ir radiation — on the order of 0 . 6 w / cm 2 . with a retinal zone of about 10 mm in diameter ( 8 mm pattern size on a lens + 1 mm on the edges due to divergence ) it corresponds to total power of 0 . 5 w on the retina . it is also possible to create a transverse focal volume 50 instead of an axial focal volume described above . an anamorphic optical scheme may used to produce a focal zone 39 that is a “ line ” rather than a single point , as is typical with spherically symmetric elements ( see fig1 ). as is standard in the field of optical design , the term “ anamorphic ” is meant herein to describe any system which has different equivalent focal lengths in each meridian . it should be noted that any focal point has a discrete depth of field . however , for tightly focused beams , such as those required to achieve the electric field strength sufficient to disrupt biological material with ultrashort pulses ( defined as t pulse & lt ; 10 ps ), the depth of focus is proportionally short . such a 1 - dimensional focus may be created using cylindrical lenses , and / or mirrors . an adaptive optic may also be used , such as a mems mirror or a phased array . when using a phased array , however , careful attention should be paid to the chromatic effects of such a diffractive device . fig1 a - 17c illustrate an anamorphic telescope configuration , where cylindrical optics 40 a / b and spherical lens 42 are used to construct an inverted keplerian telescope along a single meridian ( see fig1 a ) thus providing an elongated focal volume transverse to the optical axis ( see fig1 c ). compound lenses may be used to allow the beam &# 39 ; s final dimensions to be adjustable . fig1 shows the use of a pair of prisms 46 a / b to extend the beam along a single meridian , shown as ca . in this example , ca is reduced rather than enlarged to create a linear focal volume . the focus may also be scanned to ultimately produce patterns . to effect axial changes , the final lens may be made to move along the system &# 39 ; s z - axis to translate the focus into the tissue . likewise , the final lens may be compound , and made to be adjustable . the 1 - dimensional focus may also be rotated , thus allowing it to be aligned to produce a variety of patterns , such as those shown in fig9 and 10 . rotation may be achieved by rotating the cylindrical element itself . of course , more than a single element may be used . the focus may also be rotated by using an additional element , such as a dove prism ( not shown ). if an adaptive optic is used , rotation may be achieved by rewriting the device , thus streamlining the system design by eliminating a moving part . the use of a transverse line focus allows one to dissect a cataractous lens by ablating from the posterior to the anterior portion of the lens , thus planing it . furthermore , the linear focus may also be used to quickly open the lens capsule , readying it for extraction . it may also be used for any other ocular incision , such as the conjunctiva , etc . ( see fig1 ). a “ track and treat ” approach is one that integrates the imaging and treatment aspect of optical eye surgery , for providing an automated approach to removal of debris such as cataractous and cellular material prior to the insertion of an iol . an ultrafast laser is used to fragment the lens into pieces small enough to be removed using an irrigating / aspirating probe of minimal size without necessarily rupturing the lens capsule . an approach such as this that uses tiny , self - sealing incisions may be used to provide a capsule for filling with a gel or elastomeric iol . unlike traditional hard iols that require large incisions , a gel or liquid may be used to fill the entire capsule , thus making better use of the body &# 39 ; s own accommodative processes . as such , this approach not only addresses cataract , but presbyopia as well . alternately , the lens capsule can remain intact , where bilateral incisions are made for aspirating tips , irrigating tips , and ultrasound tips for removing the bulk of the lens . thereafter , the complete contents of the bag / capsule can be successfully rinsed / washed , which will expel the debris that can lead to secondary cataracts . then , with the lens capsule intact , a minimal incision is made for either a foldable iol or optically transparent gel injected through incision to fill the bag / capsule . the gel would act like the natural lens with a larger accommodating range . it is to be understood that the present invention is not limited to the embodiment ( s ) described above and illustrated herein , but encompasses any and all variations falling within the scope of the appended claims . for example , materials , processes and numerical examples described above are exemplary only , and should not be deemed to limit the claims . multi - segmented lens 30 can be used to focus the beam simultaneously at multiple points not axially overlapping ( i . e . focusing the beam at multiple foci located at different lateral locations on the target tissue ). further , as is apparent from the claims and specification , not all method steps need be performed in the exact order illustrated or claimed , but rather in any order that accomplishes the goals of the surgical procedure . while preferred embodiments of the present invention have been shown and described herein , it will be obvious to those skilled in the art that such embodiments are provided by way of example only . numerous variations , changes , and substitutions will now occur to those skilled in the art without departing from the invention . it should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention . it is intended that the following claims define the scope of the invention and that methods and structures within the scope of these claims and their equivalents be covered thereby .
a system for ophthalmic surgery on an eye includes : a pulsed laser which produces a treatment beam ; an oct imaging assembly capable of creating a continuous depth profile of the eye ; an optical scanning system configured to position a focal zone of the treatment beam to a targeted location in three dimensions in one or more floaters in the posterior pole . the system also includes one or more controllers programmed to automatically scan tissues of the patient &# 39 ; s eye with the imaging assembly ; identify one or more boundaries of the one or more floaters based at least in part on the image data ; iii . identify one or more treatment regions based upon the boundaries ; and operate the optical scanning system with the pulsed laser to produce a treatment beam directed in a pattern based on the one or more treatment regions .