u . s . pat . no . 7 , 115 , 120 , the contents of which are incorporated herein by reference , discloses the use of optical methods for detecting the onset of cavitation . specifically , a photodetector detects a backscatter signal from the tissue . since tissue in which cavitation occurs is more reflective , one can use the magnitude of the backscattering signal as a basis for determining the onset of cavitation . a difficulty with known methods of detecting cavitation arises from their reliance on human intervention . the clinically observable indications of cavitation are often subtle and can vary significantly from one patient to the next . thus , the known methods are difficult to automate in part because it is difficult to identify and program any bright - line rule to reliably detect the onset of cavitation . identification of bubble formation by manual examination is insufficient for cavitation detection in a clinical setting . rather , a computer algorithm that alerts the ophthalmologist to the existence of cavitation is preferred . a method to test the local threshold in an irradiation site by using small test spots prior to application of therapeutic irradiation to a large area could also be beneficial . as shown in fig1 , a scanning system 10 for in vivo illumination of the rpe with laser light is assembled on top of an ophthalmic slit lamp 12 . by placing a continuous wave ( cw ) laser 14 and all optical and mechanical components on the slit lamp 12 , one avoids the need for fiber delivery . a mirror 16 disposed in front of the objective lenses 18 of the slit lamp 12 aligns the laser beam on a collinear path with the slit lamp &# 39 ; s optical axis . the scanner system 10 preserves all the slit lamp &# 39 ; s degrees of freedom . its focal plane is carefully aligned to coincide with the slit lamp &# 39 ; s imaging plane . as a result , the slit lamp 12 is configured to be used as a targeting device for the scanning system 10 . in response to instructions from a controller 20 , an acousto - optic modulator 22 modulates the collimated output of the laser 14 . polarization of the laser beam is rotated to 45 °, for example by a half - wave plate 24 . after passing through the half - wave plate 24 , the laser light enters a polarizing beam splitter cube 26 and a faraday rotator 28 . the faraday rotator 28 further rotates the polarization of the beam to produce a horizontal polarization state for an acousto - optic deflector 30 that scans the laser beam in response to instructions from the controller 20 . a telecentric post - scanning beam expander 32 then expands the beam by a magnification m . the beam ultimately reaches a focusing lens 35 , which focuses it onto the retina 37 . a suitable laser 14 is a 532 nm laser having an output power of 1 w and a beam diameter of 1 . 6 mm . in one embodiment , the laser 14 is a ventus laser manufactured by laser quantum of cheshire , uk , the aom 22 is a tem - 85 - 1 - 0 . 532 manufactured by brimrose of baltimore , md ., and the slit lamp 12 is an sl - 130 manufactured by carl zeiss of oberkochen , germany . in one embodiment , the acousto - optic deflector 30 is a 2ds - 100 - 35 - 0 . 352 manufactured by brimrose of baltimore , md ., and the focusing lens 35 is a 125 mm lens , such as the bfpl manufactured by cvi of albuquerque , n . mex ., which has been v - coated at 532 nm to minimize reflection . on its return path , the backscattered light of the treatment beam from the retina 37 is collected by the focusing lens 35 and relayed to the telecentric beam expander 32 , which now compresses the beam diameter of the backscattered light by a factor of 1 /( magnification m ) to 5 mm , thereby matching the active aperture of the acousto - optic deflector 30 . as a result , backscattered light can be accepted over a larger cross section of the focusing lens 35 . specifically , backscattered light can be collected with a numerical aperture m times the numerical aperture of the treatment beam . this improves photon collection efficiency , which increases in proportion to the square of the numerical aperture . in one embodiment ( shown in fig1 ), the beam diameter is expanded by a factor of m = 3 from 1 . 6 to 4 . 8 mm in diameter for the radiation light ; the corresponding irradiation numerical aperture is about 0 . 02 . because of the decompression 1 / m = 1 / 3 , backscattered light can be accepted across a 15 mm diameter . this results in a collection numerical aperture of 0 . 06 , which in turn results in is an increase in photon collection efficiency by a factor of 9 . the backscattered light is then de - scanned in the acousto - optic deflector 30 and passed again through the faraday rotator 28 . this results in a 90 ° polarization mismatch between the treatment radiation and the backscattered light in the polarizing beam splitter cube 26 . the polarizing beam splitter cube 26 then directs the backscattered light onto a confocal pinhole 34 , which leads to a photodetector 36 , such as a photodiode , an avalanche photodiode , or a photomultiplier tube . the output voltage of the photodetector 36 is amplified by an amplifier 38 and sampled by a data acquisition unit 40 for ultimate storage in a tangible form on a computer - readable medium 42 . in one embodiment , the confocal pinhole 34 is a 100 μm diameter pinhole that leads to an avalanche photodiode 36 , such as the c5460 manufactured by apd of hamamatsu , japan , the data acquisition unit 40 is a gage 1250 card manufactured by compuscope of lachine , quebec , and the controller 20 for controlling the aom and aod is an arbitrary two - channel function generator , such as the afg 320 manufactured by teletronix of beaverton , oreg . in a scanning system 10 , the amount of energy deposited on a particular location in the rpe is controlled to ensure that heat generated as a result of laser energy absorbed at a particular location does not spread significantly into adjacent locations . a suitable amount of energy to be deposited at a location is that required to cause microcavitation . as a result , the reliable detection of microcavitation is a desirable feature of the scanning system 10 . because of its transient nature , microcavitation results in a transient increase in backscattering from the rpe . however , measurement of the backscattering does not lend itself to objectivity and often requires the subjective assessment of a clinician . to avoid these disadvantages , the controller 20 implements a procedure for relying on the rate of change of backscattering with respect to time . such an algorithm depends on the time derivative of the backscatter signal , or any estimate or approximation thereof , such as a numerically determined slope of the backscatter signal . reliance on the rate of change of the backscatter signal , rather than on the signal itself , eliminates variation in signal amplitude , which depends on both the instantaneous laser power and on tissue backscattering . the latter is difficult to compensate for because it can vary not only across different patients but also across different areas within one eye . because the cavitation bubble grows rapidly ( bubble lifetime is on the order of 100 ns ) the intensity between two sequential data points changes rapidly . thus , the rate of change of backscattering provides a more prominent marker of the onset of microcavitation . a measurement of the rate of change of a backscatter signal delivers large slope values that can be compared against a threshold . theoretically , a backscattering signal without cavitation has a flat derivative ( slope value v ′= 0 v / s ) while a signal with cavitation has some maximum slope value v ′& gt ; 0 v / s . in practice , system noise causes non - cavitation signals to have a range of derivative values . nevertheless , backscattering signals associated with cavitation have a significantly larger derivative than signals associated with system noise . moreover , derivatives of cavitation - related signals are separated from derivatives of non - cavitation - related signals by a gap . thus , one can readily define a threshold slope value v ′ th that reliably distinguishes cavitation from non - cavitation signals ( fig1 ). in particular , traces with v ′& gt ; v ′ th are likely to be cavitation signals , while traces with v ′& lt ; v ′ th are dominated by system noise . with the instrument shown in fig1 a threshold slope value v ′ th of at least 1 . 2 v / 40 ns is suitable . in one practice , shown in fig2 , the system determines the correct dosage by causing the laser to deposit a selected amount of energy , referred to herein as “ test dosage ,” on each of a plurality of test spots , or locations ( step 40 ). the plurality of test locations can all be within a test region , or they can be scattered about the treatment region . in one particular practice , shown in fig3 a to 3c , there are five test locations 52 disposed on a square test region 54 in a pattern similar to that found on a playing die . the test region 54 can be adjacent to a treatment region 56 , as shown in fig3 a , or it can overlap the treatment region , as shown in fig3 b and 3c . in the latter case , the treatment region 56 can encompass the test region 54 , as shown in fig3 b , or the test region 54 can encompass the treatment region 56 as shown in fig3 c . referring back to fig2 , for each test location 52 , the controller determines whether microcavitation has occurred ( step 42 ). the determination can be carried out by using the derivative of the backscatter signal . the controller then counts how many of the test locations exhibited microcavitation ( step 44 ). if that number is below a predetermined percentage of test locations j selected to indicate a laser dose that is statistically sufficient to kill a desired percentage of targeted cells ( step 46 ), the controller increases the test dosage ( step 48 ) and repeats the procedure . on the other hand , if the number of test locations 52 that exhibited microcavitation is in excess of the predetermined percentage j , the controller 20 recognizes that the dosage is adequate for treatment . in that case , the controller 20 causes the beam to move into and treat the treatment region 56 ( step 50 ). treatment can be performed by continuously scanning the laser beam , thereby forming a picket fence of scanlines . alternatively , treatment can be performed by moving the beam into discrete locations within the treatment region , thereby forming a checkerboard pattern of locations , each of which corresponds to a pulse . in an optional step , during treatment , the controller 20 monitors the derivative of the backscatter signal to confirm that microcavitation of the treatment locations is proceeding as expected . as disclosed herein , the procedure relies in part on testing to see whether the number of test locations experiencing micro cavitation at a given dosage is in excess of a predetermined percentage . however , one can achieve the same result by other comparisons . for example , one might compare the number of test locations not experiencing micro cavitation to see if that number is less than , rather than greater than , some threshold . or one might compare reciprocals of these numbers . to encompass these various mathematical manipulations , all of which achieve essentially the same result , the term “ inequality relationship ” is used to indicate the existence of a value and a threshold , both of which indicate the existence or onset of microcavitation , and both of which are elements of an ordered set of numbers . as such , there will inherently exist an inequality relationship between the value and the threshold , and that inequality relationship can be used as a basis for detecting the onset of microcavitation . another example of a scan pattern , shown in fig4 , consists of three discretely stepped pulses followed by a continuously scanned line formed by a continuously scanning beam . shown below the scan pattern in fig4 are waveforms for controlling the acousto - optic modulator 22 and acousto - optic deflector 30 to produce the illustrated scan pattern . the velocity of the continuously scanning beam is adjusted to match the pulse duration τ p of the discretely stepped pulses , i . e . the scan velocity equals one spot diameter per τ p . this results in all locations receiving the same dosage . an effective way to measure the scan velocity is to pass the spot formed by the scanning beam over the crosshairs of a microscope scale and to detect the transmitted light with a fast photodiode . since each cross hair of the scale casts a shadow on the photodiode , the time difference between adjacent cross hairs separated by a known distance provides an accurate basis for measuring velocity . based on this measurement , the controller 20 adjusts the controlling waveform to cause the pulse duration in the test region to be equal to the scanning dwell time in the treatment region 56 . the steps described above in connection with various methods for collecting , processing , analyzing , interpreting , and displaying information can be implemented in computer programs using standard programming techniques . such programs are designed to execute on programmable computers or specifically designed integrated circuits , each comprising an electronic processor , a data storage system ( including memory and / or storage elements ), at least one input device , and at least one output device , such as , for example a display or printer . the program code is applied to input data ( e . g ., measurements of capacitive coupling , measurements of ambient light intensity , and / or measurements of reflected light intensity from objects ) to perform the functions described herein . each such computer program can be implemented in a high - level procedural or object - oriented programming language , or an assembly or machine language . furthermore , the language can be a compiled or interpreted language . each such computer program can be stored on a computer or other machine readable storage medium ( e . g ., cd rom or magnetic diskette ) that when read by a computer or other machine can cause the processor in the computer to perform the analysis and control functions described herein . experiments were performed in a total of fifteen eyes of eight dutch belted rabbits . cell damage and cavitation thresholds were measured in twelve eyes . rabbits were anesthetized with a mixture of ketamine and xylazine ( 30 - 40 mg / kg + 6 - 20 mg / kg ) by intramuscular injection in the hind legs . the pupils were dilated with tropicamide 1 %, and subsequently with phenylephrine 5 %. a 25g ½ ″ butterfly was inserted into the ear vein for injection of fluorescein . each rabbit was placed in a holder system that allowed rotation and tilt of the animal with respect to the slit lamp . an ophthalmic goldmann contact lens was placed on the rabbit &# 39 ; s eye , using methylcellulose 2 % as contact gel , and held in place by a flexible telescopic arm . the corneas of non - treatment eyes were protected by applying the ophthalmic contact gel , methylcellulose 2 %, and a contact lens . under slit lamp examination , six marker lesions , purposely coagulating the neural retina , were placed in the fundus using five adjacent lines of slow continuously scanning laser exposure (˜ 100 mw ) to allow proper orientation and field determination . the test scan patterns were then placed in columns between the marker lesions at various laser powers . each scan pattern was applied only once to each irradiation site . the pulse duration and scanning speed were adjusted such that each spot within the exposed area was irradiated for 1 , 5 , 10 , 20 , and 40 μs . one parameter was tested per eye . one eye of each rabbit was treated per day ; the other eye was treated two days later . each parameter was tested in at least two eyes of different rabbits , to account for inter - subject variability . during each irradiation , the backscattering from the retina was recorded simultaneously and analyzed in post - processing to determine whether bubble formation occurred within the rpe . the location of each applied scan pattern and the applied laser power were carefully recorded to enable correlation of backscattering signals with individual exposures . immediately after each irradiation , the fundus was examined for whitening that indicates thermal coagulation of the neural retina . test lesions that became visible immediately after exposure were noted as ophthalmoscopically visible . the test field of the fundus was imaged with a color digital camera mounted on the slit lamp , and captured on a computer . the rabbit fundus was examined 45 minutes after irradiation with reflectance imaging and fluorescein angiography using a scanning laser ophthalmoscope ( slo ; hra2 , heidelberg engineering , heidelberg , germany ). high - resolution reflectance images at 488 nm were acquired to reveal possible morphological changes in the retina that may not have been visible in slit lamp examination . fluorescein angiography ( fla ) is the current standard for detecting laser - mediated damage to the distal blood - ocular barrier , which consists of the rpe and bruch &# 39 ; s membrane and separates the retina from the vasculature of the choroid . in regions where rpe cells have been damaged by the laser exposure , the blood - occular barrier will be compromised and fluorescein can leak into the subretinal space . for fluorescein angiography , a bolus of 1 ml of 10 % fluorescein sodium ( diluted 1 : 3 in phosphate buffered saline ) was injected into the ear vein of the rabbit via the butterfly . the fluorescein leakage was recorded for evaluation and documentation . for data analysis , the scan pattern was treated as two distinct entities , i . e . the pulsed and continuously scanned portions of the scan pattern were evaluated separately . fig5 a shows the fundus in rabbits following a 20 μs exposure . retinal whitening that was visible in slit lamp examination immediately after the exposure marked the ophthalmoscopically visible endpoint . similarly , high - resolution reflectance imaging showed lesions from pulsed and scanned irradiation in fig5 b as sharp white structures . the visibility of lesions in reflectance imaging is likely due to morphological changes that may not be strictly confined to rpe cells . the visibility of a lesion in the fluorescein angiogram indicated the cell damage or angiographic endpoint ( fig5 c ). fig5 c is a fluorescein angiogram showing lesions not visible in fig5 a and 5b . these lesions , which are in the middle and left columns of fig5 c and which are visible in neither the reflectance nor slit lamp images , are the desired selective lesions . the backscattering raw traces for each individual exposure were examined for the presence of a transient voltage increase that represents the endpoint for cavitation . cavitation was correlated with cell death to identify how frequently cell death is associated with bubble formation . in addition , the raw traces were differentiated to both aid in the determination of bubble formation and to explore the possibility of automated cavitation detection . endpoints were evaluated using the probit method . in probit analysis , the lognormal fit through binary response data (“ 1 ” for success , “ 0 ” for no success ) is calculated and the cumulative density distribution of the percentage of targets that do respond to an applied dose is plotted versus the dose . thus , probit analysis was performed to determine both the probability distribution as a function of laser power and the effective dose 50 % ( ed 50 ) for each parameter and endpoint . the ed 50 describes the dose required to accomplish an endpoint with a probability of 50 % and is commonly referred to as the threshold . response data were set equal to ‘ 1 ’ for each individual cell in the pulsed portion of the scan pattern when the respective endpoint had been reached , while for evaluation of the continuous scans occurrence of the endpoint was indicated anywhere within the scan line . thus , the pulsed portion of the scan field was treated as three individual events and the continuous scan portion as one individual event . data analysis was based on a total of 1149 pulses and 383 continuous scans . the threshold radiant exposure was computed from the corresponding threshold power for each endpoint . for pulses , the radiant exposure is the incident power multiplied by the pulse duration and divided by the area of the laser spot on the retina . for the continuous scan , the radiant exposure h was determined on the scan axis as previously described by where p is the incident power , τ is the dwell time and d 0 is the spot diameter . a safety margin above the angiographic threshold can be important in selective targeting . this margin is commonly referred to as the therapeutic window and is defined as the ratio of the doses that lead to 15 % probability of ophthalmoscopically visible retinal whitening ( ed 15ophth ) and the 85 % probability of angiographically visible cell death ( ed 85fla ) ( tw = ed 15ophth / ed 85fla ). selective rpe cell damage was accomplished in vivo in experimental rabbits for most parameters . cavitation was detected routinely by monitoring the backscattering of the treatment laser beam . cells were damaged predominantly by cavitation with exposures equal or shorter than trt rpe . the number of cells killed without detected cavitation increased with exposure duration . the setup generated a scan pattern comprised of three discretely stepped pulses , spaced about 110 μm apart in air , followed by a continuously scanned line that was 200 μm long , as illustrated in fig4 . it has been shown that the use of a goldman contact lens on a rabbit eye demagnifies all distances by a factor of 0 . 66 . therefore , the spacing between pulses and the length of the scan line were calculated to be about 75 μm and 130 μm on the retina , respectively . the scan speed was measured in air to be within 10 % of the corresponding pulse duration . the use of acousto - optical devices and polarization optics resulted in a maximum power on the cornea of 400 mw . the spot diameter ( 1 / e 2 ) in air was about 21 μm with a time - diffraction - limit - factor m 2 of 1 . 3 , corresponding to a retinal beam diameter of about 14 μm . the depth of focus , defined as twice the rayleigh range ( i . e . the distance over which the beam &# 39 ; s waist radius increases by a factor of 2 1 / 2 ), was 1 . 3 mm . experimentally , the beam diameter was measured in air to increase by about 1 μm over a distance of ± 200 μm away from the focal plane , as shown in fig6 , which shows spot diameter and beam propagation around the focal plane of the scanner . as is apparent from fig6 , the 1 / e 2 spot diameter in air was 21 μm , which corresponded to a retinal spot size of 14 μm . data points and error bars represent the mean and standard deviation of 12 measurements , fitted with an m 2 of 1 . 3 . the dotted line represents a fit using m 2 = 1 for comparison . rpe cell damage was routinely accomplished with laser power on the order of 100 mw as shown in table 1 below : the probit slope values ( s = ed 85 / ed 50 ) account for the width of the probability distributions and ranged from 1 . 2 to 1 . 8 for the pulses and from 1 to 1 . 6 for the scans . intracellular cavitation was detected as a transient increase in backscattering signal . cell damage and cavitation threshold powers were about equal in 5 μs pulses and in 10 μs scans . bleeding in the retinal space that would have indicated a rupture of bruch &# 39 ; s membrane was never observed . lesions were never visible with slit lamp or reflectance examination for 1 and 5 μs exposures , regardless of the irradiation mode . whitening of the retina , indicating thermal denaturation of the retina , was only observed in continuous scans and never in individual pulses ; consequently , the ophthalmoscopic threshold and therapeutic window were only given for scanning exposures . intracellular cavitation was detected by monitoring the backscattering from the retina . as an example , for exposure times close to the rpe thermal relaxation time ( trt rpe ), fig7 b and 7c show two representative fluorescein angiography images with corresponding backscattering traces for 5 μs exposures . fig7 b and corresponding backscatter signal in fig7 a are below the cell damage threshold . as shown in fig7 b , two out of three pulses and the continuous scan line damaged rpe cells at 25 % below ed 50fla . the corresponding backscattering traces in fig7 a show transient increases in detector voltage for all three pulses and within the scan line . thus , a bubble was detected in the center pulse that was insufficient to damage the cell . fig7 c and corresponding backscatter signals in fig7 d show results of radiation at about ed 50fla . in this case , rpe cells were killed in all three pulses and in a fraction of the scan line , as shown in fig7 c . the corresponding backscattering traces show cavitation throughout the pattern , shown in fig7 d . in most 1 and 5 μs exposures , cavitation correlated with cell death . exceptions were due to cavitation being detected in surviving cells . fig8 a to 8d show an example of exposure duration much longer than trt rpe ( 40 μs ). at threshold , all three pulses and the continuous scan were able to damage rpe cells , as seen by the fluorescein leakage in the fluorescence angiogram , shown in fig8 b . however , cavitation was only detected in the first pulse , as shown in the accompanying backscatter signal in fig8 a . the three pulses and the scan line successfully damaged rpe cells at 1 . 5 ed 50fla , as shown in fig8 c . this is consistent with cavitation in all backscattering traces for this exposure , as shown in the corresponding backscatter signal in fig8 d . overall , dead cells without detected cavitation were found in exposures with duration longer than trt rpe . based on these results , the thresholds for cell damage and cavitation were computed . both threshold radiant exposures were about equal for 5 μs pulses and increased with exposure duration for both pulses ( fig9 a ) and continuous scans ( fig9 b ). in the continuous scans , the threshold for cavitation was smaller than the cell damage threshold for 1 and 5 μs exposures . beginning with 10 μs exposures , the cavitation threshold was higher than that for cell damage regardless of the irradiation mode . the thresholds further diverged with increasing exposure duration . both thresholds increased more sharply for pulsed exposure . as a result , higher radiant exposure was required to damage cells and induce cavitation in pulses as compared to scans in long exposure durations . the ratio of pulsed over scanned ed 50fla was about one for 1 and 5 μs exposures , and diverged with increasing exposure duration to 1 . 4 with 40 μs exposures . the therapeutic window , determined by slit lamp examination , was about 4 for 40 μs scans and increased with shorter dwell times ( 4 . 6 with 10 μs ). even at the highest available laser power of 400 mw , no retinal whitening was observed for either 5 or 1 μs scans or in any pulses . threshold determination alone may not be sufficient , in some embodiments , to identify how frequently cavitation correlates with cell death because both dead cells without detected bubble formation and living cells that endured cavitation contribute to the probability distribution . to identify the correlation between cavitation and cell death , the percentage of dead cells that were associated with cavitation was determined for each parameter and irradiation mode . as shown in fig1 a , cavitation was detected in all dead cells for 1 and 5 μs exposures in a range from 25 % below to 50 % above cell damage threshold . at ed 50fla , the percentage of dead cells accompanied by cavitation decreased with increasing exposure duration to about 40 % at 40 μs . similarly , the percentage of cells that survived a cavitation event was also determined . as shown in fig1 b , as many as 33 % of all surviving cells were associated with cavitation in 1 μs pulses . for longer pulses , cavitation was detected in about 5 % of live cells . in the scanning portion of the scan pattern , the percentage of cavitation in surviving cells was on the order of 20 % and no live cells were associated with cavitation for scans slower than 10 μs . in order to investigate the relationship between cavitation in pulses and cell death in continuous scans , the percentage of continuous scans that successfully damaged cells was evaluated as a function of cavitation in the pulses of the same pattern . the results are summarized in fig1 . as indicated by fig1 , if cavitation was detected in all three pulses of the pattern , the continuous scan line killed cells in more than 90 % of all trials . the percentage decreased to between 65 % and 85 % with 1 or 10 μs pulses , respectively , when bubble formation was observed in only one out of three pulses . on the basis of this data , it is reasonable to conclude that test pulses can be used to measure the local threshold in particular test location in a test site before a therapeutic , large - area scan is applied to a treatment location in a treatment site . the derivative of the backscattering signal traces aided in the determination of bubble formation . fig1 e shows the maximum derivatives of 1 , 5 and 10 us pulses at multiples of the ed 50fla . maximum derivatives of transient voltage increases due to cavitation ranged from larger than 1 . 2 v / 40 ns to up to 50 v / 40 ns ; slopes larger than 6 v / 40 ns were omitted for clarity . in backscattering traces without cavitation , the derivative was dominated by system noise and was smaller than 1 . 2 v / 40 ns . thus , cavitation and non - cavitation signals were separated by a threshold value of 1 . 2v / 40 ns . most derivatives shown in fig1 a - 12d indicate cavitation or no cavitation . less than 2 % of all evaluated derivatives fall within a region of ± 0 . 2 v / 40 ns of the threshold . fig1 a - 12d show representative backscattering traces with their corresponding derivatives close to the threshold , for 1 and 5 μs pulses , respectively . in fig1 a , a backscattering signal with a derivative of 1 . 16 v / 40 ns would be classified as displaying no cavitation . in fig1 b , a signal having a derivative of 1 . 28 v / 40 ns would be classified as a signal indicative of cavitation . both of the 5 μs traces in fig1 c and fig1 d would be classified as showing cavitation , because their derivatives are 1 . 2 and 1 . 8 v / 40 ns , respectively . the feasibility of optically detecting intracellular cavitation during selective targeting of the rabbit rpe has been investigated using the system shown in fig1 . the scan pattern generated three discretely stepped pulses followed by a continuously scanned line with clinically crucial exposure durations ranging from 1 to 40 μs . selective rpe cell damage was accomplished with moderate laser power on the order of 100 mw . the absence of visible lesions both under slit lamp examination and using high - resolution reflectance imaging with an slo suggests that 1 and 5 μs exposures are safe for selective targeting with a therapeutic window that is at least 5 . 4 regardless of the irradiation mode . intracellular cavitation was detected routinely by monitoring the backscattered light of the treatment laser beam . cell death was accompanied by cavitation with irradiation on the order of the thermal relaxation time in duration , suggesting that the cell damage mechanism is photo - mechanical for 1 and 5 μs pulses and scans . with increasing exposure time , the cell damage mechanism undergoes a gradual transition to a more photo - thermal mode as an increasing number of cells are killed without detected cavitation . this study confirms in an in vivo model that intracellular cavitation , detected by monitoring the backscattering from the target tissue , can reliably report rpe cell damage for exposure durations of at least up to 10 μs . moreover , the derivative of backscattering traces with or without cavitation are separated by a fixed threshold value for all exposure durations and for both irradiation modes . therefore , a simple computer - based comparator can automatically distinguish between cavitation and non - cavitation based on the maximum derivative of the backscattering traces . furthermore , cavitation in the pulsed portion of the scan pattern correlates with cell death in the scans . as a result , test pulses can be utilized in a scanner to measure and predict the local cell damage threshold , before a large - area therapeutic scan is applied . the foregoing techniques are applicable to the control of dosimetry for individual irradiation sites in eyes with varying optical characteristics and clarity . it is to be understood that the foregoing description is intended to illustrate and not limit the scope of the disclosure , which is defined by the scope of the appended claims . other aspects , advantages , and modifications are within the scope of the following claims .
methods and systems for controlling selective targeting of retinal pigment epithelium cells within a treatment region of the rpe . the methods include depositing a selected amount of energy on a test region of the rpe ; determining an extent to which microcavitation has occurred in the test region ; and on the basis of the determination , either depositing the selected amount of energy on the treatment region , or depositing an increased amount of energy on the test region , and repeating steps and .