U.S. patent application number 13/948678 was filed with the patent office on 2013-12-26 for system and method for generating treatment patterns.
This patent application is currently assigned to Topcon Medical Laser Systems, Inc. The applicant listed for this patent is Topcon Medical Laser Systems, Inc. Invention is credited to Dan E. Anderson, Katrina Bell, Justin Hendrickson, George Marcellino, David Haydn Mordaunt, Michael W. Wiltberger.
Application Number | 20130345683 13/948678 |
Document ID | / |
Family ID | 37889527 |
Filed Date | 2013-12-26 |
United States Patent
Application |
20130345683 |
Kind Code |
A1 |
Mordaunt; David Haydn ; et
al. |
December 26, 2013 |
SYSTEM AND METHOD FOR GENERATING TREATMENT PATTERNS
Abstract
A method of treating target tissue of an embodiment comprises:
selecting a treatment pattern of spots; generating an aiming beam
of aiming light; translating the aiming beam to form an aiming
pattern of the aiming light on the target tissue that indicates the
extent of the treatment pattern; generating a treatment beam of
treatment light; and translating the treatment beam to form the
selected treatment pattern of spots of the treatment light on the
target tissue.
Inventors: |
Mordaunt; David Haydn; (Los
Gatos, CA) ; Marcellino; George; (Santa Cruz, CA)
; Wiltberger; Michael W.; (Santa Clara, CA) ;
Hendrickson; Justin; (Carlisle, MA) ; Bell;
Katrina; (Palo Alto, CA) ; Anderson; Dan E.;
(Menlo Park, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Topcon Medical Laser Systems, Inc |
Santa Clara |
CA |
US |
|
|
Assignee: |
Topcon Medical Laser Systems,
Inc
Santa Clara
CA
|
Family ID: |
37889527 |
Appl. No.: |
13/948678 |
Filed: |
July 23, 2013 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
11523392 |
Sep 18, 2006 |
|
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|
13948678 |
|
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|
|
60718762 |
Sep 19, 2005 |
|
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60758169 |
Jan 10, 2006 |
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Current U.S.
Class: |
606/4 |
Current CPC
Class: |
A61B 2018/2272 20130101;
A61F 9/00823 20130101; A61B 2018/2025 20130101; A61F 2009/00863
20130101; A61F 2009/00878 20130101; A61F 9/00821 20130101; A61B
2018/2266 20130101; A61F 2009/00897 20130101; A61B 2018/2035
20130101; A61F 9/008 20130101; A61B 2018/20359 20170501 |
Class at
Publication: |
606/4 |
International
Class: |
A61F 9/008 20060101
A61F009/008 |
Claims
1. A method of treating target tissue, comprising: selecting a
treatment pattern of spots; generating an aiming beam of aiming
light; translating the aiming beam to form an aiming pattern of the
aiming light on the target tissue that indicates the extent of the
treatment pattern; generating a treatment beam of treatment light;
and translating the treatment beam to form the selected treatment
pattern of spots of the treatment light on the target tissue.
2. The method of claim 1, wherein the aiming beam is translated to
form an enclosed aiming pattern of the aiming light on the target
tissue in which the treatment pattern is to be confined.
3. The method of claim 2, wherein the enclosed aiming pattern
outlines the treatment pattern.
4. The method of claim 2, wherein the shape of the enclosed aiming
pattern comprises any one of a circle, rectangle and ellipse.
5. The method of claim 1, wherein the aiming beam is translated to
form the aiming pattern that indicates the outer perimeter of the
treatment pattern.
6. The method of claim 1, wherein the aiming pattern further
indicates a center position of the treatment pattern.
7. The method of claim 6, wherein the shape of the aiming pattern
comprises a crossed line.
8. A photomedical system for treating target tissue, comprising: a
treatment light source configured to generate a treatment beam of
treatment light; an aiming light source configured to generate an
aiming beam of aiming light; a scanner assembly configured to
translate the treatment beam to form a treatment pattern of spots
of the treatment light on the target tissue, and translate the
aiming beam to form an aiming pattern of the aiming light on the
target tissue that indicates the extent of the treatment pattern;
and a controller configured to control the scanner assembly.
9. The photomedical system of claim 8, wherein the scanner assembly
is configured to translate the aiming beam to form an enclosed
aiming pattern of the aiming light on the target tissue in which
the treatment pattern is to be confined.
10. The photomedical system of claim 9, wherein the enclosed aiming
pattern outlines the treatment pattern.
11. The photomedical system of claim 9, wherein the shape of the
enclosed aiming pattern comprises any one of a circle, rectangle
and ellipse.
12. The photomedical system of claim 8, wherein the scanner
assembly is configured to translate the aiming beam to form the
aiming pattern that indicates the outer perimeter of the treatment
pattern.
13. The photomedical system of claim 8, wherein the aiming pattern
further indicates a center position of the treatment pattern.
14. The photomedical system of claim 13, wherein the shape of the
aiming pattern comprises a crossed line.
Description
[0001] This application is a division of U.S. patent application
Ser. No. 11/523,392 filed Sep. 18, 2006, which claims the benefit
of U.S. Provisional Application No. 60/718,762, filed Sep. 19,
2005, and of U.S. Provisional Application No. 60/758,169, filed
Jan. 10, 2006, all of which are hereby incorporated by reference in
their entirety.
FIELD OF THE INVENTION
[0002] The present invention relates to retinal photocoagulation,
and more particularly to a system and method for patterned optical
ophthalmic treatment.
BACKGROUND OF THE INVENTION
[0003] Presently, conditions such as diabetic retinopathy and
age-related macular degeneration are subject to photocoagulative
treatment with visible laser light. While this type of visible
laser light treatment halts the progress of the underlying disease,
it can be problematic. For example, because the treatment entails
exposing the eye to visible laser light for a long period of time
(typically on the order of 100 ms), damage can be caused to the
patient's sensory retina from the heat that is generated. During
the treatment, heat is generated predominantly in the retinal
pigmented epithelium (RPE), which is the melanin-containing layer
of the retina directly beneath the photoreceptors of the sensory
retina.
[0004] Although light is absorbed in the RPE, this type of
treatment irreversibly damages the overlying sensory retina and
negatively affects the patient's vision.
[0005] Another problem is that some treatments require the
application of a large number of laser doses to the retina, which
can be tedious and time consuming. Such treatments call for the
application of each dose in the form of a laser beam spot applied
to the target tissue for a predetermined amount of time. The
physician is responsible for ensuring that each laser beam spot is
properly positioned away from sensitive areas of the eye that could
result in permanent damage. Since some treatments can require
hundreds of laser beam spots to evenly treat the target tissue, the
overall treatment time can be quite long and require great
physician skill to ensure an even and adequate treatment of the
entire target tissue area.
[0006] To reduce the treatment time needed for retinal
photocoagulation, a system and method has been proposed for
applying multiple laser spots automatically in the form of a
pattern of spots, so that an area of target tissue is efficiently
treated by multiple spots pre-positioned on the tissue in the form
of the pattern. See for example U.S. Patent Publication
US2006/0100677. However, rapid delivery of multiple beam spots in
patterns raises new issues. For example, localized heating can
occur with the rapid and consecutive delivery of adjacent beam
spots within a pattern. Moreover, variations in the patterns are
needed to provide better exclusion zone and beam spot density
control (both for even density and variable density), as well as
better system control through a graphic user interface.
SUMMARY OF THE INVENTION
[0007] An embodiment solves the aforementioned problems by
providing a method of treating target tissue comprises steps of:
selecting a treatment pattern of spots; generating an aiming beam
of aiming light; translating the aiming beam to form an aiming
pattern of the aiming light on the target tissue that indicates the
extent of the treatment pattern; generating a treatment beam of
treatment light; and translating the treatment beam to form the
selected treatment pattern of spots of the treatment light on the
target tissue.
[0008] Additionally, a photomedical system for treating target
tissue of an embodiment comprises: a treatment light source
configured to generate a treatment beam of treatment light; an
aiming light source configured to generate an aiming beam of aiming
light; a scanner assembly configured to translate the treatment
beam to form a treatment pattern of spots of the treatment light on
the target tissue, and translate the aiming beam to form an aiming
pattern of the aiming light on the target tissue that indicates the
extent of the treatment pattern; and a controller configured to
control the scanner assembly.
[0009] Other objects and features of the present invention will
become apparent by a review of the specification, claims and
appended figures.
BRIEF DESCRIPTION OF THE DRAWINGS
[0010] FIG. 1 is a schematic diagram of the scanning coagulation
system.
[0011] FIG. 2 is a diagram of a pattern P of a single spot.
[0012] FIGS. 3A-3G are diagrams of symmetrical patterns P of
spots.
[0013] FIGS. 4A-4F are diagrams of non-symmetrical patterns P of
spots.
[0014] FIGS. 5A-5B are diagrams of patterns P of spots with fully
enclosed exclusion zones.
[0015] FIGS. 6A-6B are diagrams of patterns P of spots with
partially open exclusion zones.
[0016] FIG. 7 is a diagram of a circular pattern P of spots having
a generally uniform spot density.
[0017] FIG. 8 is a diagram illustrating the scanning order of a
pattern P of spots with adjacent spots scanned consecutively.
[0018] FIGS. 9A and 9B are diagrams illustrating adjacent spots
from a single pattern P separated into two different spot
patterns.
[0019] FIG. 9C is a diagram illustrating the pattern P of spots
resulting from the combination of patterns in FIGS. 9A and 9B.
[0020] FIGS. 10A-10B are diagrams of a pattern P of spots with
adjacent spots having different sizes.
[0021] FIGS. 11A and 11B are diagrams illustrating two different
scanning orders of a round pattern P of spots.
[0022] FIGS. 12A and 12B are diagrams illustrating two different
scanning orders of a wedge shaped pattern P of spots.
[0023] FIGS. 13A and 13D are diagrams illustrating four separately
scanned sub-patterns that together form scanned pattern P.
[0024] FIGS. 14A-14D are diagrams illustrating aiming patterns that
either enclose the area in which the treatment pattern P of spots
of will be positioned or identify the center and outer extent of
the treatment pattern P.
[0025] FIGS. 15A-15D are diagrams illustrating aiming patterns that
either enclose the area in which the treatment pattern P of spots
of will be positioned or identify the center and outer extent of
the treatment pattern P.
[0026] FIG. 16 is a diagram illustrating automatic generation of
arc patterns.
[0027] FIG. 17 is a front view of a graphic user interface screen
for operating the photocoagulation system.
[0028] FIG. 18 is a front view of the graphic user interface screen
displaying multiple possible pattern configurations from which to
choose from.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0029] The present invention is a system and method for generating
patterns P of aiming and treatment light on target eye tissue (e.g.
the retina) of a patient's eye. FIG. 1 depicts an ophthalmic slit
lamp based scanning photocoagulator 1, which is a non-limiting
example of a photocoagulation system for creating and projecting
aiming and/or treatment patterns of spots onto a patient's retina
R. System 1 includes a light source assembly 2 and a slit lamp
assembly 3.
[0030] The light source assembly 2 includes a treatment light
source 12 for generating an optical beam of treatment light 14, and
an aiming light source 16 for generating an optical beam of aiming
light 18. Treatment beam 14 from treatment light source 12 is first
conditioned by lens 20, which is used in conjunction with a curved
mirror 22 to prepare treatment beam 14 for input into an optical
fiber bundle 24. After encountering lens 20, treatment beam 14 is
sampled by partially reflecting mirror 26. The light reflected from
mirror 26 is used as an input for a photodiode 28 that monitors the
output power of treatment beam 14, assuring that the light source
12 is operating at the desired power. A mirror 30 is used to steer
treatment beam 14 onto mirror 22, which in turn directs treatment
beam 14 onto moving mirror 32. Aiming beam 18 from aiming light
source 16 is directed onto moving mirror 32 via mirrors 34 and
36.
[0031] Moving mirror 32 is preferably mounted on a galvanometric
scanner (but could also be moved by piezo actuators or other well
know optic moving devices), and moves to selectively direct
treatment and aiming beams 14, 18 to one of the optical fibers 24a,
24b, 24c, 24d of optical fiber bundle 24 at any given time, where
lenses 42, 44 focus the treatment and aiming beams 14, 18 into the
selected optical fiber(s). Preferably, moving mirror 32 is spaced
one focal length away from lens 20 to provide for a telecentric
scan condition (thus allowing for the injection of treatment beam
14 into all the optical fibers 24a-24d on parallel paths, which
preserves the launch numerical aperture across the optical fiber
bundle 24). Adjacent to the optical fibers 24a-24d are beam dumps
38, 40, which provide convenient locations to "park" the treatment
beam 14. Optical fibers 24a-24d are used to deliver the treatment
and aiming beams 14, 18 from the light source assembly 2 to the
slit lamp assembly 3. An additional optical fiber 46 may be used to
direct the treatment and/or aiming beams 14, 18 to the patient via
other means such as an endoprobe or laser indirect ophthalmoscope
(not shown).
[0032] Slit lamp assembly 3 includes an optical fiber input 50 (for
receiving optical fibers 24a-24d), a scanner assembly 52, a
delivery assembly 54, and a binocular viewing assembly 56. The
optical fiber input 50 preferably includes a unique optical
conditioning system for each of the optical fibers 24a-24d, so that
each optical fiber can produce a specific (and preferably unique)
spot size at the image plane IP of the slit lamp assembly 3. For
example, light from optical fiber 24a first encounters a lens 58a
that collimates the light, followed by an aperture 60 that serves
to reduce the effective numerical aperture by obscuring all but the
central portion of the light beam. Light from optical fibers 24b
through 24d first encounter lenses 58b through 58d, respectively.
Lenses 58b-58d are preferably configured to create different spot
sizes at the image plane IP, and subsequently at the target tissue
(retina R). In the illustrated example, optical fibers 24a and 24b
have the same core diameter, but are made to create different spot
sizes by using different lenses 58a and 58b. Optical fibers 24c and
24d have different core diameters. It is preferable (but not
necessary) that all optical fibers deliver light with the same
numerical aperture. Therefore, to keep the operating numerical
apertures identical for these different channels, aperture 60 is
used to counteract the change in optical power of lens 58a relative
to lenses 58b, 58c, 58d.
[0033] The optical output of each optical fiber 24a-24d after
conditioning by the associated optical systems (e.g. lenses
58a-58d, aperture 60, etc.) is directed to the scanner assembly 52,
which includes two movable mirrors 62, 64 mounted to two
galvanometers 66, 68 (although any well known optic moving device
such as piezo actuators could be used). Mirrors 62, 64 are
configured to rotate in two orthogonal axes to scan (i.e.
translate) the incoming light to form any desired pattern P. Mirror
62 may be rotated to redirect the light from any given one of the
fibers 24a-24d into the remainder of slit lamp assembly 3, thus
acting to "select" the output from that optical fiber while
prohibiting any light from the other optical fibers to continue
through the entire slit lamp assembly 3. Because the output ends of
optical fibers 24a-24d are not coincident, mirror 62 must be
rotated into position to intercept the light from the desired
optical fiber and transmit that light to mirror 64, which can
further move the light in an orthogonal axis. This configuration
has the added benefit of preventing any stray light that may be
delivered by the non-selected optical fibers from exiting the
system. In FIG. 1, optical fiber 24b is shown as the selected
fiber, where the output of this fiber is scanned by mirrors 62, 64
to create a scanned pattern of light that travels through the rest
of the system.
[0034] The scanned pattern of light P (which originates from
treatment light source 12 and/or aiming light source 14) leaving
the scanner assembly 52 passes through the delivery assembly 54,
which includes lens 70 (for creating the intermediate scanned
pattern at image plane IP), lens 72 (for conditioning the light
pattern for focusing into the eye), mirror 74 (for directing the
light pattern toward the target eye tissue), lens 76 (preferably an
infinity-corrected microscope objective lens) and lens 78
(preferably a contact lens that provides final focusing of the
pattern of light P onto the target eye tissue such as the retina
R). Illumination source 80 (such as a halogen light bulb) is used
to illuminate the target eye tissue R so that the physician can
visualize the target eye tissue.
[0035] The user (i.e. physician) views the target eye tissue R
directly via the binocular viewing assembly 56, which includes
magnification optics 82 (e.g. one or more lenses used to magnify
the image of the target eye tissue, and preferably in an adjustable
manner), an eye safety filter 84 (which prevents potentially
harmful levels of light from reaching the user's eye, and which may
be color-balanced to provide for a photopically neutral
transmission), optics 86, and eyepieces 88.
[0036] Pattern P of light is ultimately created on the retina of a
patient R using optical beams 14, 18 from treatment light source 12
and aiming light source 16 under the control of control electronics
90 and central processing unit (CPU) 92. Control electronics 90
(e.g. field programmable gate array, etc.) and CPU 92 (e.g. a
dedicated microprocessor, a stand-alone computer, etc.) are
connected to various components of the system by an input/output
device 94 for monitoring and/or controlling those components. For
example, control electronics 90 and/or CPU 92 monitor photodiode 28
(to ensure treatment beam 14 is generated at the desired power
level), operate the light sources 12, 16 (turn on/off, set power
output level, etc.), operate mirror 32 (to select which optical
fiber will be used for treatment and/or aiming beams 14, 18), and
control the orientations of galvanometric scanners 66, 68 to
produce the desired pattern P on the target eye tissue. CPU 92
preferably serves to support control electronics 90, and serves as
input for a graphical user interface (GUI) 96 and an alternate user
input device 98. GUI 96 allows the user to command various aspects
of the system, such as the delivered spot size and pattern, pulse
duration and optical power output from treatment light source 12
and aiming light source 16. In addition to the user physically
moving slit lamp assembly 3 for gross alignment, the ultimate fine
alignment of the light pattern P on the target tissue may be
further controlled by use of the input device 98 (which can be a
joystick, a touchpad, etc.), which causes mirrors 62, 64 alter
their rotations when scanning the light beam thus translating the
entire pattern P on the target tissue. This approach yields very
fine control of the disposition of the scanned beam. Additional
input devices 98 can be included, such as knobs to adjust the
output power of the light sources 12, 16, a footswitch or other
type of activation device to activate the application of the aiming
pattern and/or treatment pattern, etc. The ultimate disposition of
the optical output of light sources 12, 16 is intended to be the
pattern P contained in the patient's retina R.
[0037] The most basic types of patterns P are those formed of
discrete, uniformly sized and uniformly spaced fixed spots. The
user can use GUI 96 to select, modify, and/or define a number of
pattern variables, such as: spot size, spot spacing (i.e. spot
density), total number of spots, pattern size and shape, power
level, pulse duration, etc. In response, the CPU 92 and control
electronics 90 control the treatment light source 12 (assuming it
is a pulsed light source) or additionally a shuttering mechanism
(not shown) somewhere along the beam 14 to create pulsed treatment
light. Mirrors 62, 64 move between pulses to direct each pulse to a
discrete location to form a stationary spot. FIG. 2 shows a pattern
P having a single spot 100. FIGS. 3A-3G show fully symmetrical
(i.e. symmetrical in both the vertical and horizontal axes) square
or circular patterns P of spots 100. FIGS. 4A-4D show
non-symmetrical patterns P of spots 100 such as lines, rectangles
and ellipses. FIGS. 5A-5B show patterns P of spots 100 with
completely enclosed exclusion zones 102, which are zones within the
pattern P that are free of spots 100. FIGS. 6A-6B show patterns P
of spots 100 with partially open exclusion zones 102, where the
exclusion zone 102 is not completely surrounded by the spots 100.
Different patterns are ideal for different treatments. For example,
a single spot pattern is ideal for titrating the power for
treatment, performing touchups to space between pattern spots, and
sealing individual micro-aneurysms. Rectangle, square and line
patterns are ideal for PRP (panretinal photocoagulation).
Elliptical and circular patterns are ideal for treating the macula,
and sealing tears. Arc patterns (i.e. circular or elliptical wedge
patterns but without a radially center portion as shown in FIG. 4F)
are ideal for partially surrounding and treating a tear, as well as
for PRP treatment for periphery and lattice degeneration. Patterns
with enclosed exclusion zones are ideal for treating around
sensitive areas such as the fovea where it is important that the
sensitive area not receive any treatment light. Patterns with
partially open exclusion zones are ideal for treating sensitive
areas that are connected to other sensitive areas, such as avoiding
treatment of both the fovea and the optic nerve that extends from
the fovea--see especially pattern P in FIG. 6A)
[0038] FIG. 7 illustrates a circular pattern P with a substantially
uniform spot density. With rectangular shaped patterns, uniform
spot density over the entire pattern P is easily achieved by making
the rows and columns equally spaced apart and spots 100 all the
same size. However, with a circular pattern, uniformity is not
easily achieved. Forming concentric circles of spots with the same
number of spots in each circle will result in a reduced spot
density as the radius increases. Therefore, the following criteria
has been developed to maximize the uniformity of the spot density
of a circular pattern P of spots 100 (where the following
calculations are preferably performed by the CPU 92): [0039] 1)
Spots 100 are positioned in N circles of different radii all
concentrically positioned around a single central point. [0040] 2)
The diameter D(n) of the nth circle of pattern P (where n=1, 2, . .
. N, and n=1 is the circle closest to the center) is:
[0040] D(n)=EZ+S.sub.D+(n-1).times.S.sub.D(.sub.8+Round(DF)) (1)
[0041] where EZ is the diameter of the desired exclusion zone if
any (i.e. desired diameter of most inner circle), S.sub.D is the
diameter of the spots, and Round(DF) is the density factor DF
rounded (up or down) to the nearest whole number. The density
factor DF is a number preferably selected or adjusted by the user
via the system GUI 96. Typical density factors for eye surgery can
be in the low single digits. If no exclusion zone is desired, then
n=2, 3, . . . N, and n=2 is the circle closest to the center [0042]
3) The number of spots 100 in the nth circle of pattern P is:
[0042] Number ( n ) = 8 .times. Round [ .pi. .times. D ( n )
.times. 1 8 .times. 1 S D .times. 1 DF ] ( 2 ) ##EQU00001## [0043]
where Round here is rounding (up or down) to the nearest whole
number. [0044] 4) If there is no exclusion zone EZ, then n=2, 3 . .
. N, with n=2 corresponding to the circle closest to the
center.
[0045] These same equations can be utilized to form constant
density concentric arcs of equal angular extent A along N
concentric circles (e.g. see FIGS. 4F, 6A, 6B). For calculating the
diameter of the circle on which the arcs lie, equation (1) is the
same, where A is the angular extent of the arcs and is between 0
and 2.pi.. The number of spots in each concentric arc is (i.e.
equation (2) becomes):
Number ( n ) = 8 .times. Round [ .pi. .times. D ( n ) .times. 1 8
.times. 1 S D .times. 1 DF .times. A 2 .pi. ] ( 3 )
##EQU00002##
[0046] The most straight forward technique for scanning spots 100
in a pattern P is sequentially where adjacent spots are scanned
consecutively from one end of the pattern to the other to minimize
the amount of scanning mirror movement between spots (as
illustrated in FIG. 8). However, exposing two adjacent spots
consecutively (one just after the other) may result in undesirable
localized heating. Thus, interlaced patterns can be used to
minimize localized heating. Interlaced patterns are patterns that
overlap each other in an alternating manner, so that the patterns
themselves overlap each other, but the spots of one pattern do not
overlap the spots of the other pattern (i.e. spots of one pattern
are positioned among the spots of the other in an alternating or
intermixed manner). FIGS. 9A and 9B represent how a pattern P
(illustrated in FIG. 9C) can be split up into two separate patterns
P.sub.1 and P.sub.2 of alternating spots, so that spots immediately
adjacent to each other in the pattern P are scanned onto the target
tissue in two separate patterns (and thus more separated in time).
In the particular example of FIGS. 9A-9C, pattern P.sub.1
represents half of the total spots in pattern P, and pattern
P.sub.2 represents the same pattern as pattern P.sub.1 except it is
rotated by a small angle (e.g. 11.25 degrees). Thus pattern P.sub.1
of FIG. 9A is scanned in its entirety, then pattern P.sub.2 of FIG.
9B is scanned in its entirety in an interlaced fashion relative to
pattern P.sub.1, thus resulting in pattern P of FIG. 9C that
induces less localized heating during its scan onto the target
tissue.
[0047] FIG. 10A illustrates a variation of the interlacing of the
two patterns P.sub.1 and P.sub.2 to result in pattern P. In this
configuration, the size of spots 100 forming pattern P.sub.2 is
smaller than that of the spots 100 forming pattern P.sub.1. Thus,
in the combined pattern P, adjacent spots have different sizes.
This has the advantage of preserving more of the untreated retina
and maintaining open space for subsequent follow-up treatment(s)
(i.e. variable dosing). FIG. 10B is a variation on FIG. 10A, in
which the spot size is consistent within the same ring, but spot
sizes from one ring to the next can vary.
[0048] FIGS. 11A-11B illustrate how varying the spot sequencing can
be used to balance control of localized heating with other
considerations. In FIG. 11A, the sequence in which each spot is
scanned is numbered. Thus, the first eight pulses are used to
consecutively scan the eight spots that form the innermost circle.
Then, the next most innermost circle is consecutively scanned, and
so on. Each circle is scanned in a single direction with adjacent
spots being scanned in consecutive order. The advantage of this
pattern sequence is that the innermost circle closest to the
exclusion zone 102 is scanned first, so that if the patient's eye
moves later on while the pattern is still being scanned, the beam
at that point in the treatment will be further away from the
sensitive eye tissue in the exclusion zone and thus will minimize
the risk of inadvertent exposure to this tissue (e.g. the fovea).
It should be noted that this spot sequence results in adjacent
spots in each circle being scanned consecutively, which may result
in undesirable localized heating. In FIG. 11B, the spot sequence is
modified so that each circle is scanned one at a time starting with
the innermost circle, but within each circle adjacent spots are not
scanned consecutively (i.e. adjacent pulses in the beam are not
used to scan adjacent spots in the final pattern). This can entail
either a random ordering, or a more orderly sequence such as
scanning every other spot as the beam traverses around the circle
(as shown in FIG. 11B).
[0049] FIGS. 12A and 12B show pulse sequencing similar to that of
FIGS. 11A and 11B, except as applied to a wedge shaped pattern P.
Specifically, in FIG. 12A, arcs of different radii are scanned one
arc at a time, in order, starting from the innermost circle. In
FIG. 12B, the spots 100 of the wedge shaped pattern P are scanned
randomly both within as well as among the different arcs.
[0050] FIGS. 13A-13D show how a larger pattern P can be broken up
into sub-patterns. Specifically, instead of scanning the entire
pattern P (in this example a circular pattern), it may be
preferable to break up the pattern P into sub-patterns (in this
example wedge-shaped quadrants), and scan each sub-pattern P.sub.1,
P.sub.2, P.sub.3, P.sub.4 in its entirety before moving on to the
next sub-pattern. Within each sub-pattern, the spots may be scanned
out of order to minimize localized heating as discussed above. The
advantage of this technique is that if the scanning were
interrupted during one sub-pattern (e.g. due to excessive eye
movement), the system can better recover by simply moving on to the
next sub-pattern. Trying to resume a partially completed scan of a
pattern may not be feasible in some applications once registration
between the scanner and the target tissue is lost. In other words,
it is easier to register the location of an entire sub-pattern and
continue rather than try to register the location of the remaining
spots within a partially completed scanned pattern. By scanning the
spots using sub-patterns to form an overall pattern P, and each
sub-pattern is scanned without scanning adjacent spots
consecutively, there is a good balance between small pattern local
working areas and avoidance of excessive localized heating.
[0051] There are various relationships that the aiming beam can
take relative to the treatment beam. For example, the aiming light
can be projected onto the target tissue in a pattern that generally
matches that of the treatment light (i.e. the system projects a
pattern P of spots with the aiming light, followed by the
projection of the pattern P of spots with the treatment light
overlapping the positions of the spots projected by the aiming
light). In this manner, the physician can align the pattern P of
treatment light spots knowing they will be positioned where the
pattern P of alignment light spots are seen on the target tissue.
Alternately, the aiming light can be scanned in a pattern P.sub.AIM
of enclosed shape (e.g. circle, rectangle, ellipse, etc.), where
the treatment light pattern P of spots will be inside that enclosed
shape (i.e. the pattern P.sub.AIM of aiming light outlines the
target tissue that will receive the treatment light pattern P).
Thus, P.sub.AIM of FIG. 14B outlines the pattern P of FIG. 14A, and
P.sub.AIM of FIG. 15B outlines the pattern P of FIG. 15A. In yet
another example, the alignment pattern P.sub.AIM can identify the
center of the treatment light pattern P of spots, and possibly
indicate the extent of the treatment light pattern P of spots (e.g.
alignment pattern P.sub.AIM is cross hairs showing the center of
the treatment light pattern P, with the outer ends of the cross
hairs indicating the outer perimeter of the treatment light pattern
P. Thus, P.sub.AIM of FIGS. 14C and 14D identify the center and
extent of the pattern P of FIG. 14A, and P.sub.AIM of FIGS. 15C and
15D identify the center and extent of the pattern P of FIG.
15A.
[0052] FIG. 16 illustrates how the system can automatically
generate pattern sizes that exceed the scan size capabilities of
the system. In FIG. 16, the desired pattern P is in the shape of a
circular arc, with four sub-arc patterns 1-4. The system can be set
to allow the user to define the innermost sub-arc pattern 1 as a
first scan, where the system will proceed to scan sub-arc pattern
1, and then automatically identify and scan in sequential order
sub-arc patterns 2, 3, 4 which are disposed radially outwardly from
the sub-arc pattern 1. With this configuration, a user can define
an arc shaped pattern that approaches the scan limits of the
system, and the system will automatically scan additional
sub-patterns disposed radially outwardly from the pattern
identified by the user.
[0053] FIG. 17 illustrates an exemplary graphic user interface
(GUI) 96 for selecting and implementing the above described
photocoagulation patterns. The illustrated GUI 96 comprises a touch
screen display 110, which defines soft keys on the screen can be
used to change the operating conditions of the system. For example,
the display 110 defines soft keys for adjusting aim beam power 112,
fixation light power 114, exposure time 116, treatment power 118,
spot density 120, pattern 122, and spot diameter 124. Touching
these soft keys allows the user to adjust the selected
parameter(s). Some soft keys are in the form of up/down arrows,
which allow the user to directly adjust the numeric value. Other
soft keys provide multiple options (e.g. spot density 120) from
which the user can select the desired option. Still other soft keys
illustrate an operating parameter, and when activated open new
menus from which to manipulate that operating parameter (e.g. the
pattern soft key 122 illustrates the configuration of the selected
pattern such as spot spacing and pattern shape and layout, and when
activated such as being touched opens a menu for selecting from a
plurality of predefined patterns as illustrated in FIG. 18, or for
defining a new pattern; the spot diameter soft key 124 indicates
the size of the spots and when touched opens a menu for adjusting
the spot size). Status indicators are also provided on display 110
(e.g. status indicator 126 indicates whether the system is in a
standby mode, an aiming light mode, or a treatment light mode;
counter indicator 128 keeps track of the number of treatment
applications and can be reset by touching the reset soft key 130).
Soft keys can also be tailored to the specific data being input.
For example, by dragging the user's finger around pattern soft key
122 allows the user to select how many quadrants, octants, etc.
that will be included in a circular pattern (e.g. dragging around
the pattern key 122 for approximately 310 degrees will select a
pattern with seven octants--i.e. one octant will be left out of an
otherwise complete circular pattern).
[0054] As used herein, the terms "comprises," "comprising,"
"includes," "including," "has," "having" or any other variation
thereof, are intended to cover a non-exclusive inclusion. For
example, a process, method, article, or apparatus that comprises a
list of elements is not necessarily limited to only those elements
but may include other elements not expressly listed or inherent to
such process, method, article, or apparatus. Further, unless
expressly stated to the contrary, "or" refers to an inclusive or
and not to an exclusive or. For example, a condition A or B is
satisfied by any one of the following: A is true (or present) and B
is false (or not present), A is false (or not present) and B is
true (or present), and both A and B are true (or present).
[0055] 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, while many of the
patterns P described above and illustrated in the figures have a
uniform spot density configuration, the present invention is not so
limited. The spot density can be varied in the same pattern P in
various ways. For example, the sizes and/or separation of spots 100
in one portion of the pattern P can be different than that in
another portion of the same pattern P.
[0056] Treatment density can also be varied in the same pattern P,
by varying the power and/or pulse duration that form spots in one
portion of the pattern P relative to the power and/or pulse
duration that spots in another portion of pattern P. Pattern P can
not only be formed of discrete stationary spots as described above,
but also by one or more moving spots that form scanned lines or
other scanned images. The aiming light source (or another light
source) can be used to project a fixation pattern on the eye along
with the aiming pattern P and/or the treatment pattern P to give
the patient a reference point to keep the eye still during
treatment. The above system is ideal for, but not limited to,
photocoagulation diagnosis/treatment. Lastly, as is apparent from
the claims and specification, not all method steps necessarily need
be performed in the exact order illustrated or claimed, but rather
in any order that allows for the proper alignment and projection of
the treatment pattern P.
* * * * *