U.S. patent application number 10/498382 was filed with the patent office on 2009-12-03 for method and apparatus for improving safety during exposure to a monochromatic light source.
Invention is credited to Michael Slatkine.
Application Number | 20090299440 10/498382 |
Document ID | / |
Family ID | 41395078 |
Filed Date | 2009-12-03 |
United States Patent
Application |
20090299440 |
Kind Code |
A9 |
Slatkine; Michael |
December 3, 2009 |
Method and apparatus for improving safety during exposure to a
monochromatic light source
Abstract
A method and apparatus are disclosed for improving bodily safety
during exposure to a monochromatic light source by diverging the
monochromatic light, such as with a highly durable diffuser. At a
first position of the distal end of the monochromatic light source
the energy density of an exit beam from said distal end is
substantially equal to the energy density of the monochromatic
light required for desired applications and at a second position of
the distal end the energy density of the light emitted therefrom is
significantly less than the energy density of the monochromatic
light. Accordingly, a laser unit suitable for aesthetic treatment,
medical treatment or industrial treatment is converted into an eye
safe laser unit. Eye safety is further enhanced by measuring the
radiance of the divergent monochromatic light and issuing a warning
as a result of a mishap if the radiance of the divergent
monochromatic light is greater than a predetermined safe value, and
if desired, generating a visible flash prior to the emission of a
pulse of monochromatic light to induce an eye of a bystander to
blink or to change its field of view in order to avoid staring at
the monochromatic light.
Inventors: |
Slatkine; Michael; (Herzlia,
IL) |
Correspondence
Address: |
PROSKAUER ROSE LLP
ONE INTERNATIONAL PLACE
BOSTON
MA
02110
US
|
Prior
Publication: |
|
Document Identifier |
Publication Date |
|
US 20050234527 A1 |
October 20, 2005 |
|
|
Family ID: |
41395078 |
Appl. No.: |
10/498382 |
Filed: |
June 10, 2004 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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PCT/IL02/00635 |
Aug 2, 2002 |
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10498382 |
Jun 10, 2004 |
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10614672 |
Jul 7, 2003 |
7184614 |
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10498382 |
Jun 10, 2004 |
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Current U.S.
Class: |
607/89 ; 601/7;
601/9 |
Current CPC
Class: |
A61B 2018/00023
20130101; A61B 2018/1807 20130101; A61B 2018/00458 20130101; A61B
2018/00452 20130101; A61B 2018/2261 20130101; A61B 2090/049
20160201; A61B 90/04 20160201; A61B 2018/00476 20130101; A61B
2017/00172 20130101; A61N 5/0616 20130101; A61B 18/203
20130101 |
Class at
Publication: |
607/089 ;
601/007; 601/009 |
International
Class: |
A61N 5/06 20060101
A61N005/06; A61H 23/02 20060101 A61H023/02 |
Foreign Application Data
Date |
Code |
Application Number |
Dec 10, 2001 |
IL |
147009 |
Jun 6, 2002 |
IL |
150094 |
Feb 22, 2004 |
IL |
160510 |
Claims
1. Method of improving bodily safety of bystanders exposed to a
monochromatic light source used for the treatment of a target,
comprising: providing an apparatus which includes said
monochromatic light source and light conveying means for conveying
the light generated by said source to said target, said conveying
means having a distal end; and causing the conveyed monochromatic
light to diverge at said distal end; whereby at a first position of
said distal end relative to a target the energy density of an exit
beam from said distal end is substantially equal to the energy
density of the monochromatic light and at a second position of the
distal end relative to a target the radiance of the light emitted
from said distal end is significantly less than the radiance of the
monochromatic light, and wherein the first position is
substantially in contact with a target to which the monochromatic
light is .directed
2. Method of claim 1, further comprising a) providing a diverging
unit transparent to the monochromatic light unit comprising at
least one focusing lens, a plurality of reflectors and a distally
positioned plate transparent to the monochromatic light; b)
attaching said diverging unit to the distal end of the light
conveying means; c) focusing the monochromatic light onto at least
one of said reflectors; and d) allowing light rays to exit said
plate at varying angles, depending on the number of times reflected
by said reflectors, whereby to cause said monochromatic light to be
divergent.
3. Method of claim 1, further comprising the steps of scattering
the monochromatic light, said scattered monochromatic light being
divergent.
4. Method of claim 3, further comprising: a) providing a diffusing
unit with a distal end, said diffusing unit comprising at least one
diffusively transmitting element, wherein each of said diffusively
transmitting elements is transparent to the monochromatic light; b)
attaching said diffusing unit to the distal end of the light
conveying means; and c) allowing the monochromatic light to be
scattered by each of said diffusively transmitting elements.
5. Method of claim 3, further comprising: a) providing a diffusing
unit transparent to the monochromatic light comprising an angular
beam expander and at least one diffuser; b) attaching said
diffusing unit to the distal end of the light conveying means; and
c) allowing the monochromatic light to propagate through said
angular beam expander and said at least one diffuser, whereby to
scatter said monochromatic light.
6. Method of claim 8, further comprising the following steps: a)
providing a diffusing unit with a plurality of diffusers, wherein
at least one diffuser is axially displaceable; b) axially
displacing said at least one axially displaceable diffuser to an
active position such that each diffuser is substantially in contact
one with the other, whereby the energy density of an exit beam from
said diffusing unit is substantially equal to the energy density of
the monochromatic light at the first position of the distal end of
the monochromatic light source; and c) axially displacing said at
least one axially displaceable diffuser to an inactive position
such that each diffuser is separated one from the other by a gap
large enough to generate a sufficiently large scattering angle such
that the energy density of the light emitted from said diffusing
unit at the second position of the distal end of the monochromatic
light source is significantly less than the energy density of the
monochromatic light.
7. Method of claim 1, wherein the energy density of the
monochromatic light is between 2 and 60 J/cm.sup.2.
8. Method of any of claims 1 to 6, wherein the radiance of the
divergent monochromatic light is less than 14 J/cm.sup.2sr.
9. Method of any of claims 1 to 6, wherein the radiance of the
divergent monochromatic light is less than 10*k1*k2*(t 1/3)
J/cm.sup.2/sr, where t is a laser pulse duration in seconds,
k1=k2=1 for a wavelength ranging from 400 to 700 nm, k1=1.25 and
k2=1 for a wavelength of approximately 750 nm, k1=1.6 and k2=1 for
a wavelength of approximately 810 nm, k1=3 and k2=1 for a
wavelength of approximately 940 nm, and k1=5 and k2=1 for a
wavelength ranging from 1060 to 1400 nm.
10. Method of claim 1, further comprising measuring the radiance of
the divergent monochromatic light and issuing a warning as a result
of a mishap if the radiance of the divergent monochromatic light is
greater than a predetermined safe value.
11. Method of claim 1, wherein the monochromatic light is selected
from the group of collimated laser beam, convergent laser beam,
concentrated multiple laser beams and fiber guided laser beam.
12. Method of claim 11, wherein the monochromatic light source is
selected from the group of Excimer, Dye, Nd:YAG 1064, 1320 and 440
nm, frequency doubled Nd:YAG, Ruby, Alexandrite, Diode including
diodes operating at a wavelength of 810 to 830 nm, 940 nm, and 1450
nm, stack of diodes, LICAF, Er:Glass, Er:YAG, Er:YSGG, CO.sub.2,
isotopic CO.sub.2 and Holmium lasers.
13. Method of claim 1, wherein the monochromatic light is provided
with a wavelength ranging from 308 to 1600 nm or between 1750 nm to
11.5 microns and the energy density level of the monochromatic
light source ranges from 0.01 to 2000 J/cm.sup.2.
14. Method of clam 1, wherein the monochromatic light source is a
plurality of monochromatic diodes.
15. Method of claim 1, wherein the bodily safety includes eye
safety, skin safety and environmental safety.
16. Method of claim 1, wherein the exit beam at the first position
is used in applications selected from the group of cosmetic
applications, medical applications an industrial applications.
17. Method of claim 1, wherein the exit beam at the first position
is used in applications selected from the group of hair removal,
coagulation of blood vessels located on a face or legs, treatment
of rosacea, tattoo removal, removal of pigmented lesions in the
skin, skin rejuvenation, treatment of psoriasis, treatment of acne,
skin resurfacing, skin vaporization, collagen contraction, dental
application, removal of pigments from the gums, teeth whitening,
dermatology, gynecology, podiatry, urology, reduction of pain,
laser welding of transparent plastic materials, surface treating of
material, laser annealing, evaporation of paint and ink stains and
cleaning of building stones, antique sculptures and pottery.
18. Method of claim 4, wherein a laser beam is controllably
repositionable to scan targets of the diffusively transmitting
element.
19. Method of claim 18, wherein the sequence of targets to be
impinged by the laser beam is programmable.
20. Method of claim 4, further comprising the following steps:
providing the diffusing unit with a clear transmitting element such
that a gap is formed between a diffusively transmitting element and
said clear transmitting element, the diffusively transmitting and
clear transmitting elements being transparent to the monochromatic
light, placing said clear transmitting element on a target skin
location, directing the monochromatic light to said target skin
location and cooling skin within said gap.
21. Method of claim 1, wherein a half angle of a divergent exit
beam at the first position exceeds 6 degrees.
22. Method of claim 4, wherein a half angle of a divergent exit
beam at the first position exceeds 42 degrees.
23. Method of claim 1, wherein the duration of a laser pulse ranges
from 1 nanosecond to 1600 msec, and the diameter of a spot size
ranges from 1 to 20 mm.
24. Method of claim 23, wherein a series of pulses is
generated.
25. Method for converting a laser source suitable for aesthetic
treatment, medical treatment or industrial treatment of a target
into an eye safe laser unit, comprising: a) connecting to said
source light conveying means for conveying the light generated by
said source to said target, said conveying means having a distal
end; b) attaching a diverging optical unit to the distal end of
said conveying means, allowing monochromatic light to propagate
through said conveying means; and c) causing the conveyed
monochromatic light to diverge at said distal end; whereby to
generate a non-coherent and diffused light emission from said
distal end at a sufficiently low radiance value such that said
light is eye safe to bystanders exposed to said light and of a
sufficiently high energy density at the target location to effect
said aesthetic treatment, medical treatment or industrial
treatment.
26. Method of claim 25, wherein the unit is a divergent diffusing
optical unit.
27. Method of cooling skin which is irradiated with monochromatic
light, comprising: a) providing a monochromatic light source with a
distal end; b) providing a unit with two transmitting elements that
are transparent to monochromatic light, such that a gap is formed
between said two elements; c) attaching said unit to the distal end
of the monochromatic light source; d) placing said unit on a skin
location to be treated; e) providing means for skin cooling, said
skin cooling means being disposed within said gap; f) allowing
monochromatic light to propagate through said unit to said skin
location, the temperature of the skin location to be treated
thereby increasing; and g) allowing said skin cooling means to cool
said skin location.
28. Method of claim 27, further comprising the following steps: a)
providing the unit with a diffusively transmitting element and with
a clear transmitting element distally positioned with respect to
said diffusively transmitting element; b) allowing the
monochromatic light to be scattered by said diffusively
transmitting element, whereby the energy density of an exit beam
from said clear transmitting element is substantially equal to the
energy density of the monochromatic light; and c) reposition the
unit from the target to a predetermined position at which the
energy density of an exit beam from said diffusively transmitting
element is significantly less than the energy density of the
monochromatic light.
29. Method of claim 28, wherein the skin cooling means is fluid
transparent to the monochromatic light, said fluid flowing through
a conduit inserted within the gap.
30. Method of claim 29, wherein the fluid is in fluid communication
with an external cooler.
31. Method of claim 27 or 28, wherein the skin cooling means is a
thermoelectric cooler, the thermoelectric cooler operative to cool
the lateral sides of the transmission element placed on the skin
location to be treated.
32. Method of improving eye safety during exposure to a
monochromatic light source, comprising: providing a monochromatic
light source and generating a visible flash prior to the emission
of a pulse of monochromatic light, thereby inducing an eye of a
bystander to blink or to change its field of view in order to avoid
staring at the monochromatic light.
33. Method of claim 32, wherein the generation of the visible flash
is synchronized to the timing of the emission of the monochromatic
light pulse.
34. Method of claim 33, wherein the duration of the pulse is
shorter than an eye blinking response time.
35. Method of claim 34, wherein the monochromatic light source is
suitable for hair removal, photorejuvenation or treatment of
vascular lesions.
36. Apparatus for improving bodily safety of bystanders exposed to
a monochromatic light source, comprising light conveying means for
conveying said light to a target and light diverging means attached
to the distal end of said light conveying means, said diverging
means being adapted to cause the monochromatic light to be
divergent, whereby at a first position of said distal end relative
to a target the energy density of an exit beam from said distal end
is substantially equal to the energy density of the monochromatic
light and at a second position of said distal end relative to a
target the radiance of the light emitted from said distal end is
significantly less than the radiance of the monochromatic
light.
37. Apparatus of claim 36, wherein the diverging means comprises a
diverging unit provided with at least one focusing lens, a
plurality of reflectors and a distally positioned plate transparent
to the monochromatic light, each of said at least one lens provided
with a suitable focal length so as to focus the monochromatic light
onto at least one of said reflectors, each of said reflectors
positioned so as to allow light rays to exit said plate at varying
angles, depending on the number of times reflected by said
plurality of reflectors, whereby to cause said monochromatic light
to be divergent.
38. Apparatus of claim 36, wherein the diverging means is also a
scattering means.
39. Apparatus of claim 38, wherein the scattering means comprises a
diffusing unit attachable to the distal end of the light conveying
means, said diffusing unit including at least one diffusively
transmitting element that is transparent to essentially coherent
monochromatic light.
40. Apparatus of claim 38, wherein the scattering means comprises a
diffusing unit attachable to the distal end of the light conveying
means, said diffusing unit including an angular beam expander and
at least one diffuser.
41. Apparatus of claim 38, wherein the scattering means comprises a
diffusing unit attachable to the distal end of the light conveying
means, said diffusing unit comprising a plurality of diffusers
wherein at least one is axially displaceable, such that at an
active position the plurality of diffusers are substantially in
contact one with the other at the first position of the distal end
of the light conveying means, and the energy density of an exit
beam from said diffusing unit is substantially equal to the energy
density of the monochromatic light, and at an inactive position
each of said diffusers is separated one from the other by a gap
such that the radiance of the light emitted from the diffusing unit
is significantly less than the radiance of the monochromatic light
at the second position of the distal end of the diffusing unit.
42. Apparatus of claim 36, wherein the first position is
substantially in contact with a target to which the monochromatic
light is directed.
43. Apparatus of any of claims 36 to 41, wherein the radiance of
the divergent monochromatic light is less than 14
J/cm.sup.2/sr.
44. Apparatus of any of claims 36 to 41, wherein the radiance of
the divergent monochromatic light is less than 10*k1*k2*(t 1/3)
J/cm.sup.2/sr, where t is a laser pulse duration in seconds,
k1=k2=1 for a wavelength ranging from 400 to 700 m, k1=1.25 and
k2=1 for a wavelength of approximately 750 nm, k1=1.6 and k2=1 for
a wavelength of approximately 810 nm, k1=8 and k2=1 for a
wavelength of approximately 940 nm, and k1=5 and k2=1 or a
wavelength ranging from 1060 to 1400 nm.
45. Apparatus of claim 36, wherein the monochromatic light is
selected from the group of collimated laser beam, convergent laser
beam, concentrated multiple laser beams and laser guided laser
beam.
46. Apparatus of claim 45, wherein the monochromatic light source
is selected from a the group of Excimer, Dye, Nd:YAG 1064, 1820 and
1440 nm, frequency doubled Nd:YAG, Ruby, Alexandrite, Diode
including diodes operating at a wavelength of 810 to 830 nm, 940
nm, and 1450 nm, stack of diodes, LlCAF, Er:Glass, Er:YAG, Er:YSGG,
CO.sub.2, isotopic CO.sub.2 and Holmium laser units.
47. Apparatus of claim 36, wherein the monochromatic light is
provided with a wavelength ranging from 308 to 1600 nm or between
1760 nm to 11.5 microns and the energy density level of the
monochromatic light source ranges from 0.01 to 2000 J/cm.sup.2.
48. Apparatus of claim 36, wherein the monochromatic light source
is a plurality of monochromatic diodes.
49. Apparatus of claim 36, wherein the bodily safety includes eye
safety, skin safety and environmental safety.
50. Apparatus of claim 36, wherein the exit beam at the first
position is used in applications selected from the group of
cosmetic applications, medical applications and industrial
applications.
51. Apparatus of claim 36, wherein the exit beam at the first
position is used in applications selected from the group of hair
removal, coagulation of blood vessels located on a face or legs,
treatment of rosacea, tattoo removal, removal of pigmented lesions
in the skin, skin rejuvenation, treatment of psoriasis, treatment
of acne, skin resurfacing, skin vaporization, collagen contraction,
dental applications, removal of pigments from the gums, teeth
whitening, dermatology, gynecology, podiatry, urology, reduction of
pain, laser welding of transparent plastic materials, surface
treating of materials, laser annealing, evaporation of paint and
ink stains and cleaning of buildings, stones, antique sculptures
and pottery.
52. Apparatus of claim 45, wherein the duration of a laser pulse
ranges from 1 nanosecond to 1500 msec.
53. Apparatus of claim 46, wherein the laser unit is provided with
a power level ranging from 1 to 2000 W, when under continuously
working operation.
54. Apparatus of claim 39, wherein the material of each diffusively
transmitting element is selected from the group of silica, glass,
sapphire, diamond, non-absorbing polymer, light diffusing polymer,
polycarbonate, acrylic, density packed fibers, NaCl, CaF.sub.2,
glass, ZnSe and BaF.sub.2.
55. Apparatus of claim 89, wherein the diffusing unit is further
provided with a clear transmitting element distal to a diffusively
transmitting element, the diffusively transmitting element and
clear transmitting elements being mutually parallel and
perpendicular to the longitudinal axis of the diffusing unit.
56. Apparatus of claim 55, wherein the clear transmitting element
is made of a material selected from the group of glass, sapphire,
transparent polymer including polycarbonate and acrylic, BaF.sub.2,
NaCl and ZnF.sub.2.
57. Apparatus of claim 55, wherein a gap between the diffusively
transmitting and clear transmitting elements is less than 2 mm.
58. Apparatus of claim 39, wherein each diffusively transmitting
element is provided with a plurality of irregularities which are
randomly distributed thereabout.
59. Apparatus of claim 39, wherein the diffusively transmitting
element is formed by a diffraction pattern or by a randomly
distributed array of thin fibers.
60. Apparatus of claim 40, wherein the diffusing unit further
comprises at least one light guide, each of sad light guides being
provided with internally reflecting walls and an exit surface.
61. Apparatus of claim 60, wherein a light guide is tapered.
62. Apparatus of claim 60, wherein a light guide is made of a
material selected from the group of solid glass, sapphire, plastic
and liquid dielectric material.
63. Apparatus of claim 60, further comprising an optical element
which increases the divergence angle of monochromatic light and a
diffuser which receives light from said optical element and emits
said received light to the light guide, the exit source of said
light guide functioning as a wide angle extended diffuser
source.
64. Apparatus of claim 39, further comprising a plurality of
reflectors, the angular disposition and distance of each reflector
relative to the diffusing unit being repositionable, whereby to
accurately direct the monochromatic light to a selected target on
the diffusively transmitting element.
65. Apparatus of claim 64, further comprising a processor, said
processor suitable for the programming of the sequence of targets
to be impinged by the monochromatic light.
66. Apparatus of claim 39, further comprising a scar for rapid
repositioning of the monochromatic light to a target on the
diffusively transmitting element.
67. Apparatus of claim 36, wherein the distance between a distal
end of the diverging means and the target at the first position of
the distal end of the monochromatic light source is the smaller of
2 mm and the diameter of the monochromatic light.
68. Apparatus of any of claims 37 to 41, wherein a unit is attached
to the distal end of the monochromatic light source by an
attachment means.
69. Apparatus of claim 68, wherein the unit is fixedly attached to
the distal end of the monochromatic light source.
70. Apparatus of claim 68, wherein the unit is integrally formed
together with the distal end of the monochromatic light source
during manufacturing, the unit being disposed internally to the
outer wall of the monochromatic light source.
71. Apparatus of claim 68, wherein the attachment means is
releasable.
72. Apparatus of claim 71, wherein the attachment means is
permanently attached to the monochromatic light source and
displaceable, whereby in one position of a displaceable unit the
monochromatic light source is coherent, not propagating through
said displaceable unit, and in a second position at which said
displaceable unit is attached to the distal end of the
monochromatic light source, the monochromatic light is noncoherent,
propagating through the displaceable unit.
73. Apparatus of claim 36, wherein a divergent angle of the
divergent monochromatic light is greater than a half angle of 6
degrees.
74. Apparatus of claim 39, wherein a half angle of a scattered exit
beam exceeds 42 degrees.
75. Apparatus of claims 37 to 41, further comprising a means to
evacuate vapors or particles from a target to thereby prevent a
change in optical properties of the unit.
76. Apparatus of claim 75, wherein the evacuation means is U-shaped
in vertical cross-transmission element, to allow for contact with a
target at its lateral ends and for evacuation of vapors or
particles through a gap formed by its central open region.
77. Apparatus of claim 76, the evacuation means further comprising
a relay optics device, whereby to concentrate the exit beam from
the unit onto the target.
78. Apparatus of claim 55, further comprising a means for skin
cooling, said skin cooling means being disposed in a gap formed
between the frosted and clear transmitting elements.
79. Apparatus of claim 36, further comprising a means for measuring
the radiance of the divergent monochromatic light, control
circuitry in communication with said measuring means and the
monochromatic light source, and a warning means in communication
with said control circuitry which is activated, as a result of a
mishap, if the radiance of the divergent monochromatic light is
greater than a predetermined safe value.
80. Apparatus of claim 36, further comprising a means for
generating a visible flash and control circuitry in communication
with said means for generating a visible flash and with the
monochromatic light source, said control circuitry synchronized
such that a flash is generated prior to the emission of each pulse
of monochromatic light.
81. Apparatus of claim 36, wherein the monochromatic light source
is one or more arrays of a diode light source.
82. Apparatus of claim 36, comprising a handpiece.
83. Apparatus for cooling skin which is irradiated with
monochromatic light, comprising: a) a monochromatic light source
with a distal end; b) a unit attachable to the distal end of the
monochromatic light source, said unit being provided with two
elements that are transparent to monochromatic light, such that a
gap is formed between said two elements; and c) a means for skin
cooling insertable within said gap, said skin cooling means adapted
to reduce the rate of increase of temperature at a target skin
location.
84. Apparatus of claim 38, wherein one element is a diffusively
transmitting element and the other element is a clear transmitting
element distally positioned with respect to said diffusively
transmitting element, whereby the energy density of an exit beam
from the diffusing unit is substantially equal to the energy
density of the monochromatic light upon placement of the diffusing
unit at a position adjacent to a target skin location and is
significantly less than the energy density of the monochromatic
light at a distance from said target.
85. Apparatus of claim 83, wherein the skin cooling means is a
fluid transparent to said monochromatic light, said fluid flowable
through a conduit inserted within the gap.
86. Apparatus of claim 85, wherein the fluid is in fluid
communication with an external cooler.
87. Apparatus of claim 85, wherein the fluid is a liquid or a
gas.
88. Apparatus of claim 83 or 84, wherein the skin cooling means is
a thermoelectric cooler, the thermoelectric cooler operative to
cool the lateral sides of the element placed adjacent to the skin
location to be treated.
89. Apparatus of any of claims 83 to 88, further comprising a
scanner, said scanner being adapted to rapidly reposition the
monochromatic light to a target on the diffusively transmitting
element, the skin cooling means capable of continuously cooling the
skin at a corresponding target skin location.
90. Apparatus for improving eye safety during exposure to a
monochromatic light source, comprising: a monochromatic light
source, a means for generating a visible flash prior to emission of
a monochromatic light, and control circuitry in communication with
said means for generating a visible flash.
91. Apparatus of claim 90, wherein the control circuitry is
synchronized such that the flash is generated prior to the emission
of each pulse of monochromatic light, thereby inducing an eye of a
bystander to blink or to change its field of view in order to avoid
staring at the monochromatic light.
92. Apparatus of claim 91, wherein the duration of the pulse is
shorter than an eye blinking response time.
93. Apparatus of claim 90, wherein the monochromatic light source
is suitable for hair removal, photorejuvenation or treatment of
vascular lesions.
Description
FIELD OF THE INVENTION
[0001] The present invention is related to the field of laser-based
light sources. More particularly, the present invention is related
to providing an eye-safe laser beam that is suitable for correcting
aesthetic and medical skin disorders that require a very high
energy density. Even more specifically, the present invention is
related to a method and apparatus for improving bodily safety
during exposure to a monochromatic light source by diverging the
monochromatic light, such as with a highly durable diffuser, which
provides the required energy density of light for desired
applications at a very short distance but is inherently safe to the
eyes of bystanders.
BACKGROUND OF THE INVENTION
[0002] Current medical and aesthetic laser systems are generally
considered as high-risk systems due to the fact that the light beam
that is emitted from these systems has only a low divergence, or
even convergence. In these systems a light beam with a high energy
density and high radiance, i.e. energy density per solid angle, is
generated, which hardly attenuates as the beam propagates through
air, or through an air-like medium, to a distant target whereat it
could cause damage to bodily tissue. In the case of a laser source
emitting visible, or near visible, light, damage could result by
burning a small portion of an eye retina, if the beam is
accidentally aimed at the eyes of a bystander. Such beam could even
cause blindness.
[0003] Potential eye damage is further increased when using near
infrared lasers which emit invisible radiation, since bystanders
are unaware that a laser beam is being fired. Also, the extremely
short pulse duration of a beam emitted by many laser systems does
not allow enough time for one to react, such as by blinking or
moving the eyes, as a result of the accidental firing of a laser
beam.
[0004] Therefore, in order to minimize the risk of damaging living
tissues, or causing other kind of damages, special, and often,
high-cost precautions must be taken. For example, such precautions
might include the use of expensive (and inconvenient to use) coated
protective eyeglass filters with very high optical density and
damage-resistant values to optical radiation (i.e. thermal and
mechanical durability). Some of the properties of such filters are
included in standard documents such as ANSI Z136.1, which is the
basic American National Standard document regarding the safety of
laser beams. A very similar basic document which sets safety
labeling standards by the food and drug administration (FDA) is
$1040.10 21 CFR Ch.1 Another document which sets manufacturing
standards for the safety of eyes is ISO 15004:1997E. Other
precautions forbid using highly reflective surfaces in a room,
where the laser system is located. Special shades and/or curtains
are also utilized for preventing an accidental laser beam from
escaping the room or facility, thereby protecting people outside
the treatment room.
[0005] Of all the risks, the risk of permanently blinding people is
the most common and severe. The currently most eye-hazardous lasers
are those referred to as a pulsed-laser. For example, a Ruby,
Nd:YAG, Alexandrite, LICAF, Diodes, Dye lasers, Erbium-Glass,
Excimer lasers, etc. are examples of a pulsed-laser. High-class
Continuous Working (CW) lasers, such as Nd:YAG, KTP and Diode
lasers (at any wavelength between 630 and 1320 nm) are also known
for their risk in causing blindness. Moreover, these lasers are at
times used for cosmetic surgery in the vicinity of the eyes, such
as for eyebrow removal or skin rejuvenation around the eyes, and
therefore such surgery causes additional risk to eye damage. Other
infrared lasers (pulsed and CW), such as diodes operating at 1445
nm wavelength, CO.sub.2 and Erbium, are also capable of causing
severe eye damage from a distance by burning the cornea due to the
strong absorption of laser beams emitted from such laser sources in
the aqueous humor of the eyeball.
[0006] There is also a risk of hair and skin burns, if the laser
units are mishandled, even if operated in remote locations. Should
a collimated laser beam hit a flammable material in the treatment
room, a fire may result.
[0007] The risks associated with coherent lasers do not stem only
from the capability to generate highly collimated beams, but also
from the capability to concentrate the entire laser energy onto a
confined surface from a distance, with the appropriate focusing
optics.
[0008] Due to the extremely high thermodynamic temperature of
lasers as electromagnetic radiation sources, as compared to the
much lower temperature of conventional non-coherent light sources,
the efficacy of optical intensity preservation during the focusing
or imaging of laser beams, is close to 100%. Conventional
non-coherent light sources, although safe to use, cannot be imaged
without substantial intensity loss.
[0009] All of the above-mentioned risks associated with visible and
near infrared lasers have led to very strict governmental
regulations regarding the operation of medical and aesthetic
laser-based systems, causing a substantial increase in the expenses
of both manufacturers and operators of these systems. According to
some of these governmental regulations, the operation of laser
devices/systems is restricted to trained and skilled personnel,
i.e. technicians or nurses under the supervision of a physician. In
many countries, non-medical personnel such as cosmeticians are not
allowed to handle laser-based systems at all. As a result the laser
cosmetic business volume is restricted to a small fraction of its
potential volume.
[0010] According to some aspects of medical and cosmetic laser
systems, the treatment is focused on selected targets at the outer
surface of the skin or within the skin. Each of these targets, for
example, hair, vascular lesions, pigmented lesions, tattoos, acne,
mild collagen -damages resulting in fine wrinkles, and sun-damaged
skins, have different optical spectral absorption characteristics.
Therefore, these applications utilize laser systems that are
capable of generating visible or near infrared light having a
wavelength within the range of 310-1600 nm. There exists,
therefore, a risk of directing a laser beam having an incorrect
wavelength to a selected treated organ/tissue, which may severely
damage this organ/tissue. Even if the organ is treated by a laser
beam having the correct wavelength, there is always a risk that the
laser beam might be mistakenly aimed to other areas, which are
highly sensitive to the selected wavelength, thereby resulting in
damage.
[0011] As opposed to laser systems, non-laser incoherent diffused
sources, such as Intense Pulsed Light (IPL) sources, which are
based on high voltage arc lamps, are generally considered to be
damage-safe from a distance, since IPL systems have a limited light
source temperature, usually in the range of 1000-10,000.degree. C.,
and are consequently of limited brightness and are not focusable to
small spots, in contrast to as high as 1,000,000.degree. C. in
laser systems. However, IPL systems have reduced spectral
selectivity due to their broad spectral bands. Consequently,
IPL-based systems offer rather limited treatment capabilities in
comparison to laser-based systems.
[0012] U.S. Pat. No. 6,197,020 and U.S. Pat. No. 6,096,029 disclose
imaging of a focusing, diffusing light plate, such as from the
distal surface of a bundle of optical fibers at a distance beyond
the system, in order to focus the beam below the tissue surface.
The systems disclosed herein are also extremely risky to the eyes
since the laser energy density is essentially preserved within a
relatively small solid angle to which an eye may be exposed, even
after having transporting the beam to a distal confined spot. As
opposed to the present invention, these two patents conform to
state of the art treatments by which the focusing of a laser beam
to subcutaneous locations beyond the distal end of the treatment
system is acceptable. The generation of a laser beam having a large
divergent solid angle is disadvantageous, according to prior art
methods, particularly since efficient imaging and focusing on the
skin or into the skin would be precluded. Also, the laser energy
density associated with these two patents is efficacious only when
the diffusing, focusing plate is at a distance from a target, and
is not efficacious when located adjacent to a target.
[0013] G. Vargas and A. J. Welch, in their article "Effects of
Tissue Optical Clearing Agents on the Focusing Ability of Laser
Light within Tissue" ("Lasers in Surgery and Medicine", Supplement
13, 2001, p. 26) describe techniques for reducing the scattering of
light energy within a tissue, in order to provide for a more
focused spot and, thus, more efficient treatment of dermal lesions.
However, as already described, there is a trade-off between the
efficiency of a laser device and the potential risk in its
operation; i.e., as the beam is more focused, the treatment becomes
more risky.
[0014] Other relevant prior art is disclosed in U.S. Pat. Nos.
5,595,568, 5,879,346, 5,226,907, 5,066,293, 5,312,395, 5,217,455,
4,976,709, 6,120,497, 5,411,502, 5,558,660, 5,655,547, 5,626,631,
5,344,418, 5,964,749, 4,736.743, 5,449,354, 5,527,308, 5,814,041,
5,595,568, 5,735,844, 5,057,104, 5,282,797, 6,011,890, 5,745,519,
and 6,142,650.
[0015] The prior art laser units are not capable of generating a
beam with a high energy level that may be used for aesthetic or
surgical procedures without presenting a risk of injury to
bystanders or damage to property, such as by igniting a fire.
[0016] It is an object of the present invention to provide a laser
beam that may be used for aesthetic or surgical procedures.
[0017] It is an object of the present invention to provide a laser
beam that overcomes the disadvantages of the prior art.
[0018] It is another object of the present invention to provide a
laser beam that is not injurious to an operator, observer or to
objects located in the vicinity of or at a distance from a
target.
[0019] It is an additional object of the present invention to
provide a laser beam that may be used for industrial
applications.
[0020] It is yet another object of the present invention to provide
a unit of optical elements that provides wide angle diffusion with
high thermal durability
[0021] Other objects and advantages of the invention will become
apparent as the description proceeds.
SUMMARY OF THE INVENTION
[0022] The present invention comprises a method of improving bodily
safety of bystanders exposed to a monochromatic light source,
comprising: providing a monochromatic light source with a distal
end, causing said monochromatic light to diverge at said distal
end, whereby at a first position of said distal end relative to a
target the energy density of an exit beam from said distal end is
substantially equal to the energy density of the monochromatic
light and at a second position of the distal end relative to a
target the energy density of the light emitted from said distal end
is significantly less than the energy density of the monochromatic
light.
[0023] As referred to herein, monochromatic light is defined as
being divergent when its exit angle from the distal end of the
monochromatic light source, or from the distal end of a diverging
unit, when used, is greater than a half angle of 6 degrees, wherein
a "half angle" is defined as the half angle measured on a plane
perpendicular to the propagation axis of a collimated beam
generated by the monochromatic light source. With such a divergent
angle, protective eyeglasses having an optical density
approximately of only 2 are required for the aesthete laser types
specified hereinafter, corresponding to a transmittance of 1%. When
the divergent half angle is 20 degrees, protective eyeglasses with
an optical density of 1 are required, corresponding to a
transmittance of 10%. When the divergent half angle is 60 degrees,
no protective eyeglasses are required.
[0024] As referred to herein, "distal" is defined as a direction
towards the exit of a monochromatic light source, or of a unit
attached to the latter, when used, and "proximate" is defined as a
direction opposite from a distal direction.
[0025] The method preferably further comprises the steps of: [0026]
a) providing a diverging unit transparent to the monochromatic
light unit comprising at least one focusing lens, a plurality of
reflectors and a distally positioned plate transparent to the
monochromatic light; [0027] b) attaching said diverging unit to the
distal end of the monochromatic light source; [0028] c) focusing
the monochromatic light onto at least one of said reflectors; and
[0029] d) allowing light rays to exit said plate at varying angles,
depending on the number of times reflected by said reflectors,
whereby to cause said monochromatic light to be divergent.
[0030] In one preferred embodiment, the method further comprises
the step of scattering the monochromatic light, said scattered
monochromatic light being divergent.
[0031] As referred to herein, "scattered" monochromatic light is
defined as light whose direction has randomly changed by reflection
or refraction from discontinuities in the medium through which it
propagates, without any substantial change in the wavelength of the
incident light.
[0032] In one aspect, scattering is accomplished by [0033] a)
providing a diffusing unit with a distal end, said diffusing unit
comprising at least one diffusively transmitting element, wherein
each of said diffusively transmitting elements is transparent to
the monochromatic light; [0034] b) attaching said diffusing unit to
the distal end of the monochromatic light source; and [0035] c)
allowing the monochromatic light to be scattered by each of said
diffusively transmitting elements.
[0036] In another aspect, scattering is accomplished by [0037] a)
providing a diffusing unit transparent to the monochromatic light
comprising an angular beam expander and at least one diffuser;
[0038] b) attaching said diffusing unit to the distal end of the
monochromatic light source; and [0039] c) allowing the
monochromatic light to propagate through said angular beam expander
and said at least one diffuser, whereby to scatter said
monochromatic light.
[0040] In one aspect, scattering is accomplished by [0041] a)
providing a diffusing unit with a plurality of diffusers, wherein
at least one diffuser is axially displaceable; [0042] b) axially
displacing said at least one axially displaceable diffuser to an
active position such that each diffuser is substantially in contact
one with the other, whereby the energy density of an exit beam from
said diffusing unit is substantially equal to the energy density of
the monochromatic light at the first position of the distal end of
the monochromatic light source; and [0043] c) axially displacing
said at least one axially displaceable diffuser to an inactive
position such that each diffuser is separated one from the other by
a gap large enough to generate a sufficiently large scattering
angle such that the energy density of the light emitted from said
diffusing unit at the second position of the distal end of the
monochromatic light source is significantly less than the energy
density of the monochromatic light.
[0044] Preferably, the first position of the distal end of the
monochromatic light source is substantially in contact with a
target to which the monochromatic light is directed.
[0045] In one aspect, the radiance of the divergent monochromatic
light is less than 14 J/cm.sup.2/sr. In another aspect, the
radiance of the divergent monochromatic light is less than
10*k1*k2*(t 1/3) J/cm.sup.2/sr, where t is a laser pulse duration
in seconds, k1=k2=1 for a wavelength ranging from 400 to 700 nm,
k1=1.25 and k2=1 for a wavelength of approximately 750 nm, k1=1.6
and k2=1 for a wavelength of approximately 810 nm, k1=3 and k2=1
for a wavelength of approximately 940 nm, and k1=5 and k2=1 for a
wavelength ranging from 1060 to 1400 nm.
[0046] As referred to herein, "radiance" is defined as the energy
density divided by solid angle, wherein energy density is radiant
energy per projected area. The value of a solid angle is given in
units of steradians, normally symbolized as "sr."
[0047] The method further comprises measuring the radiance of the
divergent monochromatic light and issuing a warning as a result of
a mishap if the radiance of the divergent monochromatic light is
greater than a predetermined safe value.
[0048] The monochromatic light is selected from the group of
collimated laser beam, convergent laser beam, concentrated multiple
laser beams and fiber guided laser beam.
[0049] The monochromatic light source is selected from the group of
Excimer, Dye, Nd:YAG 1064, 1320 and 1440 nm, frequency doubled
Nd:YAG, Ruby, Alexandrite, Diode including diodes operating at a
wavelength of 810 to 830 nm, 940 nm, and 1450 nm, stack of diodes,
LICAF, Er:Glass, Er:YAG, Er:YSGG, CO.sub.2, isotopic CO.sub.2 and
Holmium lasers.
[0050] The monochromatic light is provided with a wavelength
ranging from 308 to 1600 nm or between 1750 nm to 11.5 microns and
the energy density level of the monochromatic light source ranges
from 0.01 to 2000 J/cm.sup.2.
[0051] In one aspect, the monochromatic light source is a plurality
of monochromatic diodes.
[0052] The bodily safety includes eye safety, skin safety and
environmental safety.
[0053] The exit beam at the first position is used in applications
selected from the group of cosmetic applications, medical
applications and industrial applications.
[0054] The exit beam at the first position is used in applications
selected from the group of hair removal, coagulation of blood
vessels located on a face or legs, treatment of rosacea, tattoo
removal, removal of pigmented lesions in the skin, skin
rejuvenation, treatment of psoriasis, treatment of acne, skin
resurfacing, skin vaporization, collagen contraction, dental
applications, removal of pigments from the gums, teeth whitening,
dermatology, gynecology, podiatry, urology, reduction of pain,
laser welding of transparent plastic materials, surface treating of
materials, laser annealing, evaporation of paint and ink stains and
cleaning of buildings, stones, antique sculptures and pottery.
[0055] In one aspect, a laser beam is controllably repositionable
to scan targets of the diffusively transmitting element, wherein
the sequence of targets to be impinged by the laser beam is
programmable.
[0056] The duration of a laser pulse ranges from 1 nanosecond to
1500 msec, and the diameter of a spot size ranges from 1 to 20 mm.
If so desired, a series of pulses is generated.
[0057] The present invention also comprises a method for converting
a laser unit suitable for aesthetic treatment, medical treatment or
industrial treatment into an eye safe laser unit, comprising
attaching a diverging optical unit to the distal end of a laser
unit, allowing monochromatic light to propagate through said unit,
generating a non-coherent and extended diffused source of light
from said unit at a sufficiently low radiance value such that said
source of light is eye safe to bystanders exposed to a
monochromatic light source and of a sufficiently high energy
density at a treatment location to effect said aesthetic treatment,
medical treatment or industrial treatment.
[0058] In one aspect, the unit is a divergent diffusing optical
unit.
[0059] The present invention also comprises a method of cooling
skin which is irradiated with monochromatic light, comprising:
[0060] a) providing a monochromatic light source with a distal end;
[0061] b) providing a unit with two transmitting elements that are
transparent to monochromatic light, such that a gap is formed
between said two elements; [0062] c) attaching said unit to the
distal end of the monochromatic light source; [0063] d) placing
said unit on a skin location to be treated; [0064] e) providing
means for skin cooling, said skin cooling means being disposed
within said gap; [0065] f) allowing monochromatic light to
propagate through said unit to said skin location, the temperature
of the skin location to be treated thereby increasing; and [0066]
g) allowing said skin cooling means to cool said skin location.
[0067] The method preferably further comprises the following steps:
[0068] a) providing the unit with a diffusively transmitting
element and with a clear transmitting element distally positioned
with respect to said diffusively transmitting element; [0069] b)
allowing the monochromatic light to be scattered by said
diffusively transmitting element, whereby the energy density of an
exit beam from said clear transmitting element is substantially
equal to the energy density of the monochromatic light; and [0070]
c) repositioning the unit from the target to a predetermined
position at which the energy density of an exit beam from said
diffusively transmitting element is significantly less than the
energy density of the monochromatic light.
[0071] In one aspect, the skin cooling means is fluid transparent
to the monochromatic light, said fluid flowing through a conduit
inserted within the gap. The fluid may be in fluid communication
with an external cooler.
[0072] In another aspect, the skin cooling means is a
thermoelectric cooler, the thermoelectric cooler operative to cool
the lateral sides of the transmission element placed on the skin
location to be treated.
[0073] The present invention also comprises a method of improving
eye safety during exposure to a monochromatic light source,
comprising: providing a monochromatic light source and generating a
visible flash prior to the emission of a pulse of monochromatic
light, thereby inducing an eye of a bystander to blink or to change
its field of view in order to avoid staring at the monochromatic
light.
[0074] Preferably, the generation of the visible flash is
synchronized to the timing of the emission of the monochromatic
light pulse, wherein the duration of the pulse is shorter than an
eye blinking response time.
[0075] The monochromatic light source is suitable for hair removal,
photorejuvenation or treatment of vascular lesions.
[0076] The present invention comprises an apparatus for improving
bodily safety of bystanders exposed to a monochromatic light
source, comprising a means attached to the distal end of a
monochromatic light source, said means adapted to cause the
monochromatic light to be divergent, whereby at a first position of
said distal end relative to a target the energy density of an exit
beam from said distal end is substantially equal to the energy
density of the monochromatic light and at a second position of said
distal end relative to a target the energy density of the light
emitted from said distal end is significantly less than the energy
density of the monochromatic light.
[0077] In one aspect, the diverging means comprises a diverging
unit provided with at least one focusing lens, a plurality of
reflectors and a distally positioned plate transparent to the
monochromatic light, each of said at least one lens provided with a
suitable focal length so as to focus the monochromatic light onto
at least one of said reflectors, each of said reflectors positioned
so as to allow light rays to exit said plate at varying angles,
depending on the number of times reflected by said plurality of
reflectors, whereby to cause said monochromatic light to be
divergent.
[0078] In one embodiment, the diverging means is also a scattering
means.
[0079] In one aspect, the scattering means comprises a diffusing
unit attachable to the distal end of the monochromatic light
source, said diffusing unit including at least one diffusively
transmitting element that is transparent to essentially coherent
monochromatic light.
[0080] The material of each diffusively transmitting element is
selected from the group of silica, glass, sapphire, diamond,
non-absorbing polymer, light diffusing polymer, polycarbonate,
acrylic, densely packed fibers, NaCl, CaF.sub.2, glass, ZnSe and
BaF.sub.2.
[0081] In one aspect, the diffusing unit is further provided with a
clear transmitting element distal to a diffusively transmitting
element, the diffusively transmitting element and clear
transmitting elements being mutually parallel and perpendicular to
the longitudinal axis of the diffusing unit.
[0082] The clear transmitting element is made of a material
selected from the group of glass, sapphire, transparent polymer
including polycarbonate and acrylic, BaF.sub.2, NaCl and
ZnF.sub.2.
[0083] A gap between the diffusively transmitting and clear
transmitting elements is preferably less than 2 mm.
[0084] Each diffusively transmitting element may be provided with a
plurality of irregularities which are randomly distributed
thereabout.
[0085] The diffusively transmitting element may also be formed by a
diffraction pattern or by a randomly distributed array of thin
fibers.
[0086] In another aspect, the scattering means comprises a
diffusing unit attachable to the distal end of the monochromatic
light source, said diffusing unit including an angular beam
expander and at least one diffuser.
[0087] An angular beam expander preferably comprises at least one
light guide, each of said light guides being provided with
internally reflecting walls and an exit surface. A light guide is
made of a material selected from the group of solid glass,
sapphire, plastic and liquid dielectric material, and may be
tapered.
[0088] An angular beam expander may also comprise an optical
element which increases the divergence angle of monochromatic light
and a diffuser which receives light from said optical element and
emits said received light to the light guide, the exit surface of
said light guide functioning as a wide angle extended diffuser
source.
[0089] In another aspect, the scattering means comprises a
diffusing unit attachable to the distal end of the monochromatic
light source, said diffusing unit comprising a plurality of
diffusers wherein at least one is axially displaceable, such that
at an active position the plurality of diffusers are substantially
in contact one with the other at the first position of the distal
end of the monochromatic light source, and the energy density of an
exit beam from said diffusing unit is substantially equal to the
energy density of the monochromatic light, and at an inactive
position each of said diffusers is separated one from the other by
a gap such that the energy density of the light emitted from the
diffusing unit is significantly less than the energy density of the
monochromatic light at the second position of the distal end of the
diffusing unit.
[0090] The duration of a laser pulse ranges from 1 nanosecond to
1500 msec.
[0091] A laser unit is provided with a power level ranging from 1
to 2000 W, when under continuously working operation.
[0092] In one aspect, the apparatus further comprises a plurality
of reflectors, the angular disposition and distance of each
reflector relative to the diffusing unit being repositionable,
whereby to accurately direct the monochromatic light to a selected
target on the diffusively transmitting element. A processor is
preferably provided, said processor suitable for the programming of
the sequence of targets to be impinged by the monochromatic light.
A scanner is also preferably provided for rapid repositioning of
the monochromatic light to a target on the diffusively transmitting
element.
[0093] In one aspect,the distance between a distal end of the
diverging means and the target at the first position of the distal
end of the monochromatic light source is the smaller of 2 mm and
the diameter of the monochromatic light.
[0094] A diffusing or diverging unit is attached to the distal end
of the monochromatic light source by an attachment means.
[0095] In one aspect, the unit is fixedly attached to the distal
end of the monochromatic light source.
[0096] In one aspect, the unit is integrally formed together with
the distal end of the monochromatic light source during
manufacturing, the unit being disposed internally to the outer wall
of the monochromatic light source.
[0097] In another aspect, the attachment means is releasable. For
example, the attachment means is permanently attached to the
monochromatic light source and displaceable, whereby in one
position of a displaceable unit the monochromatic light source is
coherent, not propagating through said displaceable unit, and in a
second position at which said displaceable unit is attached to the
distal end of the monochromatic light source, the monochromatic
light is noncoherent, propagating through the displaceable
unit.
[0098] Preferably, the apparatus further comprises a means to
evacuate vapors or particles from a target to thereby prevent a
change in optical properties of the unit. The evacuation means is
U-shaped in vertical cross-transmission element, to allow for
contact with a target at its lateral ends and for evacuation of
vapors or particles through a gap formed by its central open
region.
[0099] In one aspect, the evacuation means further comprising a
relay optics device, whereby to concentrate the exit beam from the
unit onto the target.
[0100] The present invention also comprises an apparatus for
cooling skin which is irradiated with monochromatic light,
comprising: [0101] a) a monochromatic light source with a distal
end; [0102] b) a unit attachable to the distal end of the
monochromatic light source, said unit being provided with two
elements that are transparent to monochromatic light, such that a
gap is formed between said two elements; and [0103] c) a means for
skin cooling insertable within said gap, said skin cooling means
adapted to reduce the rate of increase of temperature at a target
skin location.
[0104] In one aspect, one element is a diffusively transmitting
element and the other element is a clear transmitting element
distally positioned with respect to said diffusively transmitting
element, whereby the energy density of an exit beam from the
diffusing unit is substantially equal to the energy density of the
monochromatic light upon placement of the diffusing unit at a
position adjacent to a target skin location and is significantly
less than the energy density of the monochromatic light at a
distance from said target.
[0105] In one aspect, the skin cooling means is a fluid transparent
to said monochromatic light, said fluid flowable through a conduit
inserted within the gap. Preferably, the fluid is in fluid
communication with an external cooler.
[0106] In one aspect, the fluid is a liquid or a gas.
[0107] In another aspect, the skin cooling means is a
thermoelectric cooler, the thermoelectric cooler operative to cool
the lateral sides of the element placed adjacent to the skin
location to be treated.
[0108] In another aspect, the apparatus comprises a scanner, said
scanner being adapted to rapidly reposition the monochromatic light
to a target on the diffusively transmitting element, the skin
cooling means capable of continuously cooling the skin at a
corresponding target skin location.
[0109] The present invention also comprises an apparatus for
improving eye safety during exposure to a monochromatic light
source, comprising: a monochromatic light source, a means for
generating a visible flash prior to emission of a monochromatic
light, and control circuitry in communication with said means for
generating a visible flash.
[0110] The control circuitry is preferably synchronized such that
the flash is generated prior to the emission of each pulse of
monochromatic light, thereby inducing an eye of a bystander to
blink or to change its field of view in order to avoid staring at
the monochromatic light.
[0111] The duration of the pulse is preferably shorter than an eye
blinking response time.
BRIEF DESCRIPTION OF THE DRAWINGS
[0112] In the drawings:
[0113] FIG. 1 illustrates a side view of various laser units
equipped with a diffusing unit, in accordance with the present
invention, wherein the delivery system shown in FIG. 1a is an
articulated arm, in FIG. 1b is an optical fiber and in FIG. 1c is a
conical light guide;
[0114] FIG. 2 illustrates a side view of the distal end of a laser
unit, showing how the diffusing unit is attached thereto, wherein
the diffusing unit is externally attached to the guide tube in FIG.
2a, is attached to a pointer in FIG. 2b, is releasably attached to
the guide tube in FIG. 2c, is integrally formed together with the
guide tube in FIG. 2d and is displaceable in FIG. 2e whereby at one
position the exit beam propagates therethrough and at a second
position the exit beam does not propagate therethrough;
[0115] FIG. 3 is a schematic diagram of various configurations of
prior art laser units, wherein FIG. 3a shows a non-scattered beam
directed by reflectors to a target, FIG. 3b shows a non-scattered
beam directed by an optical fiber to a target, FIG. 3c illustrates
prior art surgery performed with a laser beam and scanner, FIG. 3d
shows the propagation of prior art refracted laser beams towards a
blood vessel, FIG. 3e shows an ablative laser beam focused on
tissue in conjunction with a scanner, and FIG. 3f shows the
formation of a crater in tissue by an ablative beam;
[0116] FIG. 4 is a schematic diagram illustrating the advantages of
employing a diffusing unit of the present invention, wherein FIG.
4a shows the relative location of the diffusing unit, FIG. 4b shows
that a collimated laser beam is transformed into a randomly
scattered beam, FIG. 4c shows that a scattered beam reduces risk of
injury to the skin and FIG. 4d shows that a collimated laser beam
reduces risk of injury to the eyes;
[0117] FIG. 5 is a schematic drawing showing the propagation of a
laser beam towards a blood vessel, wherein FIG. 5a shows the
propagation of an unscattered laser beam towards a blood vessel,
FIG. 5b shows the propagation of a scattered laser beam towards a
blood vessel, FIG. 5c illustrates the formation of an ablation by
means of an unscattered laser beam. FIG. 5d illustrates the
formation of an ablation by means of an scattered laser beam in
accordance with the present invention, and FIG. 5e illustrates the
scattering of a laser beam distant from a blood vessel;
[0118] FIG. 6a is a schematic drawing showing the accumulation of
liquid residue on a diffusively transmitting element and FIG. 6b is
a schematic drawing in which a diffusively transmitting element is
shown to be mounted within a hermetically sealed diffusing
unit;
[0119] FIG. 7 illustrates the production of a plurality of
microlenses, wherein FIG. 7a illustrates the sandblasting of a
metallic plate, FIG. 7b illustrates the addition of a liquid
sensitive to ultraviolet light, FIG. 7c illustrates the removal of
the metallic plate and FIG. 7d illustrates the generation of a
scattered laser beam through the microlenses;
[0120] FIG. 8 illustrates two types of a diffusing unit, wherein
FIG. 8a illustrates one employing a single wide angle diffuser and
FIG. 8b illustrates one employing a small angle diffuser;
[0121] FIG. 9 illustrates a diffusing unit which employs a tapered
light guide, such that the light guide receives monochromatic light
from an optical fiber in FIG. 9a and from an array of microlenses
in FIG. 9b;
[0122] FIG. 10 illustrates a diffusing unit which utilizes an
angular beam expander without a light guide in FIG. 10a and with a
light guide in FIG. 10b;
[0123] FIG. 11 illustrates a diffusing unit which employs two
holographic diffusers, each of which is attached to a corresponding
light guide;
[0124] FIG. 12 illustrates a diffusing unit which includes two
diffusers, one of which is axially displaceable, wherein FIG. 12a
illustrates the unit in an active position and FIG. 12b in an
inactive position;
[0125] FIG. 13 is a schematic drawing of another preferred
embodiment of the present invention in which a scanner rapidly
repositions a coherent laser beam onto a plurality of targets on a
diffusively transmitting element;
[0126] FIG. 14 is another preferred embodiment of the present
invention in which a non-scattering diverging unit is used to
diverge an input laser beam, wherein FIG. 14a illustrates a single
optical element and FIG. 14b illustrates a plurality of
elements;
[0127] FIG. 15 is a schematic diagram of various means of cooling
skin during laser-assisted cosmetic surgery, wherein FIGS. 15a-d
are prior art means, while FIG. 15e utilizes cooling fluid and FIG.
15f utilizes a thermoelectric cooler;
[0128] FIG. 16 illustrates an eye safety measurement device;
and
[0129] FIG. 17 is a schematic drawing of a flashing device, wherein
FIG. 17a illustrates one that induces uncontrolled blinking before
firing a laser beam, FIG. 17b is a timing diagram corresponding to
the flashing device of FIG. 17a, and 17c illustrates a flashing
device that detects a retroreflected beam from an eye within firing
range of a laser beam.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0130] FIG. 1a illustrates a high-intensity laser unit, generally
designated by 10, which is suitable for use with the present
invention. Laser unit 10 operates at a wavelength ranging between
300 and 1600 nm or between 1750 nm and 11.5 microns, either pulsed,
with a pulse duration of 1 nanosecond to 1500 milliseconds and an
energy density of 0.01-200 J/cm.sup.2, or continuous working with a
power density higher than 1 W/cm.sup.2. Laser unit 10 is provided
with a diffusing unit, generally designated by 15, which induces
the exit beam to be scattered. An exit beam is considered to be
scattered according to this embodiment when its average half angle
angular divergence is greater than 42 degrees relative to the
propagation axis of collimated beam 4. A half angle of 60 degrees
corresponds to the half angle generated by an "ideal transmitting
diffuser," which herein refers to a diffuser with 100% transmission
and is provided with Lambertian angular scattering properties. Such
a scattering angle, in accordance with the present invention,
allows the light which exits diffusing unit 15 to be safe to the
eyes of a bystander, yet is provided with a sufficiently high
energy density which is necessary for the clinical efficacy of the
laser unit.
[0131] Laser unit 10 comprises amplifying medium 1 activated by
power supply 2 for increasing the intensity of a light beam and two
parallel mirrors 3 that provide feedback of the amplified beam into
the amplifying medium, thereby generating a coherent beam of
ultrapure frequency. The laser unit emits a coherent beam 4 which
propagates through a delivery system 5 to distal end 6. The
delivery system depicted in FIG. 1a is articulated arm 7a.
Diffusing unit 15 is fixedly attached to the distal end of guidance
tube 12 by attachment means 16, which may be a set of screws or by
bonding or other means known to those skilled in the art, thereby
inducing non-coherent randomly scattered beam 14 associated with a
narrow spectral bandwidth that does not present any risk of damage
to bodily tissue if the laser is inadvertently directed to an
incorrect target. The diffusing unit includes a passive refractive
element that preserves the wavelength of coherent beam 4, as well
as its narrow bandwidth, which is generally less than one
Angstrom.
[0132] In one preferred embodiment of the invention, diffusing unit
15 is preferably cylindrical or rectangular, although any other
geometrical shape is equally suitable, and comprises diffusively
transmitting element 13, which is proximate to distal end 6 of the
laser unit and clear transmitting element 17. Both diffusively
transmitting element 13 and clear transmitting element 17 have the
same dimensions and are bonded to diffusing unit 15. Diffusively
transmitting element 13 and clear transmitting element 17 are
preferably separated by narrow gap 18. Due to the existence of gap
18, the laser beam will remain scattered even if clear transmitting
element 17 shatters, thereby preserving the inherent safety of a
laser unit that incorporates the present invention. The width of
gap 18 is as small as possible, usually 0.1 mm. However, diffusing
unit 15 may be adapted to a configuration in which diffusively
transmitting element 13 contacts clear transmitting element 17.
Alternatively, diffusing unit may be provided without a clear
transmitting element, whereby the frosted surface of diffusively
transmitting element 13 faces the laser unit and its smooth surface
faces the tissue.
[0133] Scattering is achieved by means of minute irregularities of
a non-uniform diameter formed on the substrate of diffusively
transmitting element 13. Diffusively transmitting element 13 is
preferably produced from thin sand blasted or chemically etched
glass, e.g. having a thickness from 0.1 to 0.2 mm, or a thin sheet
of non-absorbing light diffusing polymer, e.g. having a thickness
of less than 50 microns, such as light diffusing polycarbonate,
Mylar or acrylic.
[0134] A diffusively transmitting element may also be produced by
using a large angle holographic diffuser such as one produced by
Physical Optics Corporation (PCO), USA, and is placed adjacent to
an additional diffuser. A holographic diffuser illustrated in FIG.
11 induces a scattering half angle, for example, of at least 40
degrees and the second diffuser additionally induces the scattering
so as to attain a scattering half angle of e.g. 60 degrees.
[0135] A diffuser which approaches an ideal transmitting diffuser
and induces a scattering half angle of 60 degrees and a scattering
solid angle of 3.14 sr may be produced from material such as
acrylic or polycarbonate by pressing the material against an
appropriate surface provided with a very dense array of Frensnel
microlenses, such as those produced by Fresnel Technologies Inc.,
USA, or by placing arrays of microlenses surfaces separated from a
light guide as depicted in FIG. 9b.
[0136] Similarly diffusively transmitting element 13 may be
produced from light diffusing paper such as transparent "Pergament"
drawing paper, and may also be produced from other materials such
as ZnSe, BaF.sub.2, and NaCl, depending on the application and the
type of laser used. Both faces of clear transmitting element 17 are
essentially planar and smooth. Clear transmitting element 17, which
is capable of withstanding the thermal stress imposed by a
scattered laser beam, is transparent and made from sapphire, glass,
a polymer such as polycarbonate or acrylic, and may be produced
from other materials as well, such as ZnF.sub.2.
[0137] Diffusively transmitting element 13 may be chilled so that
it will be capable of withstanding the high power densities which
are necessary for attaining clinical efficacy.
[0138] As depicted in FIG. 1b, the delivery system may also be
optical fiber 7b into which laser beam 4 is focused. Diffusing unit
15 is mounted on guidance tube 8, which directs the beam exiting
the distal end of optical fiber 7b by attachment means 16.
Furthermore, as depicted in FIG. 1c, the laser unit may be
comprised of array 11 of miniature lasers, such as those provided
with high power diode lasers, e.g. the Lightsheer produced by
Coherent, USA, for hair removal. The beam delivery system for this
configuration is preferably conical reflector 7c. In this
configuration, diffusing unit 15 is fixed to distal end 6 of light
guide 7c and transforms a high-risk beam into randomly scattered
beam 4.
[0139] FIG. 2 illustrates various methods by which diffusing unit
15 is attached to a laser unit. In FIG. 2a, bracket 19 which
supports diffusing unit 15 is attached to guidance tube 12 of an
existing laser unit, such as one in use in a clinic, by attachment
means 16a, which may be a set of screws or by bonding. As shown in
FIG. 2b the laser unit is provided with pointer 31, or any other
equivalent subdiffusing unit which enables the user to direct beam
4 to a desired target on the skin, by the focal length and beam
diameter which are dictated by lens 9 mounted within guidance tube
12. In this alternative, diffusing unit 15 may be externally
attached to guidance tube 12, or may be attached to pointer 19. In
FIG. 2c, diffusing unit 15 is attached to Velcro tape 16c, or
another type of adhesive tape. This type of attachment means is
sufficient for temporary usage. In FIG. 2d, diffusing unit 15 is
integrally formed together with guidance tube 12 during
manufacturing, internal to the outer wall thereof. FIG. 2e
illustrates a releasable attachment means, whereby in one position
of a displaceable diffusing unit the exit beam is coherent, not
propagating through a diffusively transmitting element, and in a
second position in which diffusing unit 15 is attached to guidance
tube 12, the exit beam is noncoherent and propagates through a
diffusively transmitting element.
[0140] In prior art cosmetic laser surgery, as shown in FIG. 3a,
laser unit 20 emits a non-scattered coherent beam 24 from distal
end 23 via reflectors 21, 22, by optical fiber 29 in FIG. 3b, or
alternatively by deflectors 27 as shown in FIG. 3c, to site 26 that
is to be treated within tissue 25. Following the surgery, a
well-defined spot is generally produced having a size of up to 20
mm, depending on the specific application and device. Furthermore,
beam 24 may be directed by means of motor 28 as shown in FIG. 3c in
those situations in which extensive surgery is desired and tissue
25 needs to be scanned. When the wavelength ranges from 310-1600
nm, i.e. ultraviolet and near-infrared, the beam is scattered into
individual rays 30, as shown in FIG. 3d, while propagating to blood
vessel 32 from site 26. Blood vessel 32 is presented as an example
and could be replaced by a hair follicle or any type of skin
lesion. At wavelengths ranging from 1750 nm to 11.5 microns, i.e.
far infrared, lasers are often used in focused pin-point ablation,
that is, having a diameter ranging from 50-200 microns at a shallow
depth of 20-150 microns, of epidermal or papillary dermal tissue in
conjunction with a scanner, as shown in FIG. 3e. The lasers are
used mainly for ablation of tissue, the formation of a crater shown
in FIG. 3f. Laser 20, which is capable of effecting the desired
surgery at a large distance between distal end 23 and target site
26 for the various applications shown in FIGS. 3a-d, nevertheless
can cause severe damage if the beam is not properly aimed.
[0141] In contrast, the present invention, which is schematically
depicted in FIG. 4, presents a much lower risk to the patient and
to observers. As shown in FIG. 4a, diffusing unit 15 is attached to
distal end 23 of the laser unit. Diffusing unit 15 transforms the
coherent, usually collimated laser beam 24 into homogeneous,
randomly scattered beam 14 shown in FIG. 4b. As a result beam 14
significantly reduces risk of injury to the skin as shown in FIG.
4c or to the eyes as shown in FIG. 4d since a collimated beam is
not directed to these parts of the body. At very short distances of
less than one tenth of the diameter of beam 24 from distal end 23,
beam 24 has not begun to completely scatter and increase its
diameter and is therefore efficacious as a means for performing
cosmetic surgery as shown in FIG. 4c, although an increase in the
laser power level may sometimes be needed to compensate for reverse
reflections from the diffusing unit into the laser unit.
Compensation, in terms of an increase in the needed power level for
the laser unit, for reverse reflections is usually be close to 16%
due to four air-glass interfaces with 4% Fresnel reflection, and at
times may attain 50%. An anti-reflection coating may be used to
reduce reflection. For laser units which operate at approximately
10-20% of their maximum energy capacity, it is possible to place
the exit plane of the diffusing unit, whether a frosted or clear
transmitting element, at a distance from the skin corresponding to
approximately 50% of the exit beam diameter.
[0142] FIG. 5 demonstrates the advantages of the present invention.
FIG. 5a illustrates conventional coherent laser beam 24 at a
wavelength of 308 to 1600 nm. The collimated beam contacts tissue
25 at a diameter of D before being scattered into individual rays
30 during propagation to target destination 32. FIG. 5b illustrates
the result of attaching diffusing unit 15 to the laser unit. When
diffusing unit 15 is disposed at a small distance from the tissue
surface, the diameter of the scattered beam which contacts tissue
25 is increased by a negligible value of .DELTA.d, assuming uniform
scattering, in comparison with the original beam diameter of D. If
the thickness t of diffusing unit 15 is less than one-tenth of
original beam diameter D, there will be a loss of less than 20
percent in the original beam energy density. Also, the refraction
angle .theta., corresponding to an index of refraction of 1.5 for
keratin, into the tissue relative to collimated beam 24, when a gap
exists between diffusively transmitting element 13 and clear
transmitting element 17, will never exceed the critical angle of 42
degrees. At a refraction angle less than this critical value,
possible additional scattering in tissue is minimized. Consequently
light intensity within the tissue is preserved, therefore generally
retaining the clinical efficacy, i.e. the ability to perform a
surgical or cosmetic procedure, of the laser unit.
[0143] Just as superficial ablation 29 is formed in tissue 25 as a
result of a high energy density beam in the 1.8 to 11.5 micrometer
spectral range as shown in FIG. 5c, a similar ablation may be
formed in tissue 25 with the use of diffusing unit 15, with the
addition of .DELTA.d, as shown in FIG. 5d. A thin spacer (not
shown) may be advantageously added in order to evacuate vapors or
smoke that has been produced during the vaporization process. Such
a spacer is e.g. U-shaped in vertical cross-transmission element,
to allow for contact with a target at its lateral ends and for
vapor evacuation along the gap formed by its central open region.
For surgical procedures with which a very fast ablation rate is
needed, e.g. 1 cm.sup.3/sec for a skin thickness of 0.1 cm, the
spacer is necessarily relatively thick and the gap between the
ablated tissue and the diffusing unit is relatively large, e.g.
approximately 20-30 mm.
[0144] When an excessive amount of smoke is produced and the exit
beam becomes diffracted before impinging on the tissue, it may be
necessary to add a relay optics device (not shown), which
regenerates the degraded exit beam between the diffusing unit and
the tissue. An optical regenerator is provided with an internal
coating, such that a new and stronger beam with the same
characteristics as the degraded beam is produced when the coating
emits light energy when stimulated by the incoming photons of the
degraded beam. Cylindrical or conical tubes internally coated with
gold with an inlet diameter equal to the exit diameter of the
diffusing unit are exemplary optical regenerators for this
application. A small smoke evacuation port is preferably drilled in
the wall of the tube.
[0145] When a long-wavelength laser, which does not focus on an eye
retina and ranges from approximately 1345 nm to 10.6 microns, is
employed, an diffusing unit may not be needed. To scatter the exit
beam, an element may be externally attached to a surface which is
in contact with the skin during a cosmetic or surgical procedure,
so that the exit beam will diverge to a large extent and ensure eye
safety from a distance of a few cm from a target, while the energy
density is sufficiently high enough to allow for clinical efficacy.
For example, a miniature 0.21 Joule/pulse Erbium laser, which
produces a spot size of 1 mm.sup.2 and generates an energy density
of 2.1 J/cm.sup.2, greater than the threshold for tissue ablation,
will be safe to the eyes from a distance of 10 cm from a target if
the beam has a divergence half angle of 45 degrees.
[0146] While the laser is an effective surgical tool when the
diffusing unit is very close to the tissue surface, safety is
ensured after the diffusing unit is repositioned so that it is
disposed at a distance of a few millimeters, depending on the laser
energy, from the tissue surface. As shown in FIG. 5e, the energy
density of scattered beam 14 which impinges upon the surface of
tissue 25 is much less than the energy density which results when
the diffusing unit is proximate to the tissue surface.
[0147] The diffusing unit is adapted to induce random scattering
despite any adverse external conditions encountered during the
surgical procedure. The most likely cause of a potential change in
rate of scattering of the laser beam passing through diffusing unit
15 results from contact with tissue. Following a surgical procedure
in which the diffusing unit contacts tissue, liquid residue 36,
such as sebum, water and cooling gel, as shown in FIG. 6a, may
accumulate on diffusively transmitting element 13. The refractive.
index of liquid residue 36 may be such that, in combination with
the refractive index of diffusively transmitting element 13,
refracted beam 38 approaches the pattern of collimated beam 24 that
impinges on the diffusing unit.
[0148] To minimize the risk of injury which may exist if the
refracted beam is nearly collimated, diffusively transmitting
element 13 is mounted within diffusing unit 15, which is preferably
hermetically sealed with sealing element 39 as shown in FIG. 6b, to
prevent the accumulation of liquid residue on the former. Clear
transmitting element 42 is attached to the distal end of diffusing
unit 15 by adhesion and by means of a spacer (not shown), and is
separated from diffusively transmitting element 13 by air gap 41.
Clear transmitting element 42 and diffusively transmitting element
13 are mutually parallel, and both are perpendicular to the
longitudinal axis of diffusing unit 15. When the air gap is less
than a predetermined value, a corresponding increase in beam
diameter due to scattering is limited, thereby ensuring a minimal
effectiveness of the radiation carried by the laser beam for
clinical applications. It would be appreciated that accumulation of
liquid residue on clear transmitting element 42 will not compromise
the inherent safety of a laser. unit equipped with a diffusing
unit. Since scattering occurs at diffusively transmitting element
13, and the combined index of refraction of air gap 41, clear
transmitting element 42 and liquid residue is not sufficient to
cause the scattered beam to be once again collimated, the inherent
safety of the laser unit is preserved. The accumulation of liquid
residue will not affect the clinical efficacy of the laser unit
since clear transmitting element 42 is held close to a target
during a surgical procedure.
[0149] An additional advantage resulting from the separation of
clear transmitting element 32 from diffusively transmitting element
13 relates to added safety. Even if clear transmitting element 42
is broken, diffusively transmitting element 13 will scatter the
laser beam.
[0150] A diffusively transmitting element, adapted to achieve
diffusing half angles greater than 45 degrees and as close as
possible to an ideal transmitting diffuser, which generates a half
angle of 60 degrees, may be produced in several ways: [0151]
Sandblasting the surface of a plate of glass, sapphire, acrylic or
polycarbonate with fine particles having a size ranging from 1 to
200 microns, depending of the wavelength of the laser beam,
comprised of, by example, aluminum oxide; [0152] Sandblasting the
surface of a mold plate with fine particles having a size ranging
from 1 to 200 microns, depending on the wavelength of the laser
beam, comprised of, by example, aluminum oxide and reproducing the
contour of the newly formed mold plate surface by pressing hot
acrylic, or other suitable material thereon; [0153] Etching the
surface of a glass or sapphire plate by chemical means, such as
with hydrogen fluoride; [0154] Etching the surface of a glass plate
with a scanned focused CO.sub.2 laser beam; [0155] Applying a thin
sheet of light-diffusing polymer, such as a polycarbonate sheet, a
light diffusing acrylic plate, Mylar high quality wax paper or
graphical "Pergament Paper" to a glass plate; [0156] Generating a
diffraction pattern on the surface of a glass or on a sheet of
acrylic or polycarbonate by means of a holographic process to
thereby control the divergence angle through the diffraction
pattern,which is preferably as large as a half angle of at least
40-45; [0157] Providing a randomly distributed array of thin
fibers, arranged e.g. in the form of a conical fiber bundle light
concentrator, such as that produced by Schott, Germany, whose
aperture is provided with an exit half angle of greater than 40
degrees.
[0158] FIG. 7 illustrates the scattering effect that is achieved by
sandblasting. As shown in FIG. 7a, metallic plate 50 is bombarded
with aluminum oxide particles 48, thereby creating a random
distribution of craters 51, each of which having a different size.
Liquid 52, which is sensitive to ultraviolet light, is spilled on
metallic plate 50 in FIG. 7b and polymerized by ultraviolet
radiation. After removal of plate 50, for reuse in the next
production batch, transparent frosted plate 53 is produced, as
shown in FIG. 7c covered on one side with a random distribution of
convex lenses 55 of miniature size. Lenses 55, which have a very
short focal length of approximately a few wavelengths, convert a
collimated laser beam into a strongly divergent beam with a
complete loss of coherence. It is possible to use a similar
technique to produce a surface with convex or concave microlenses
57, as shown in FIG. 7d. Microlenses may be produced as well by
pressing melted acrylic onto a multimicrolens mold, instead of
using a UV curing technique.
[0159] As described above, an exit beam from a laser unit is
randomly scattered by a diffusing unit. One type of a diffusing
unit is a single wide angle diffuser as shown in FIG. 8a and
comprises a diffusively transmitting element 781 which produces
scattered light 782 from laser beam 780 having a wide diffusing
angle of T. Another type of diffusing unit is shown in FIG. 8b,
wherein wide angle diffusion is attained by using divergent optical
element 783, and at least one diffuser 784 and
refractive/reflective element 785. With this type of diffusing
unit, a wide diffusing angle of T is generated in three stages:
optical element 783 produces wide angle divergent beam T.sub.1 from
laser beam 780, diffuser 784 produces a small diffusing angle of
T.sub.2, and refractive/reflective element 785 expands angle
T.sub.2 to achieve wide diffusing angle T. Such a multi-component
diffusing unit may achieve a wide diffusing angle with the use of
elements of high thermal resistance and durability. It will be
appreciated that refractive/reflective element 785 may not
necessarily be distally disposed with respect to diffuser 784, and
may be configured in any other way in order to achieve wide
diffusing angle T.
[0160] FIG. 9 illustrates another preferred embodiment of- a
diffusing unit, designated as numeral 200. Diffusing unit 200 is a
wide angle diffusing unit, i.e. one that generates a scattering
angle that approaches that of an ideal transmitting diffuser, yet
is capable of enduring high power laser levels by using glass made
of small angle diffusers. Such a diffusing unit is advantageously
employed in those applications for which high energy densities are
needed for clinical efficacy, and accordingly only a wide-angle
scattering angle can ensure eye safety.
[0161] As depicted in FIG. 9a, optic fiber 201 is disposed adjacent
to the proximate end of tapered light guide 202, such that light
rays 203 that exit from fiber 201 with half angle divergence A
impinge the inner wall of light guide 202. Rays 203 then are
reflected from the inner wall of the light guide at an increasingly
smaller reflection angle R. The inner wall is coated with a
reflective coating so that reflection angle R will be less than the
critical angle for total internal reflection. The tapering angle
and the dimensions of the light guide as well as the distance of
the fiber from the light guide are selected so that exit half angle
C of diffused light 208 which propagates from distal end 204 of the
light guide is at least 60 degrees. Also, the distance between
fiber 201 and distal end 204 is selected so that the energy density
of rays 207 emitted from fiber 202 to distal end 204 without any
reflection from the light guide wall will be sufficiently low to be
considered eye safe when scattered from small angle diffuser 205,
e.g. 10 degrees, which induces a relatively small scattering angle
and is proximately placed with respect to distal end 204 of the
light guide. A small angle diffuser is advantageously selected due
the availability of such diffusers, its high durability and
capability to withstand a high energy density, as required for
aesthetic and industrial applications. Small angle diffuser 205
increases the divergence of diffused light 208, in addition to the
divergence generated by tapered light guide 202.
[0162] In an exemplary diffusing unit, fiber 201 induces a half
angle divergence of 25 degrees, the distance from fiber 201 to
light guide 202 is 16 mm, the inner diameter of light guide 202 at
its proximate end is 15 mm, the tapering angle of light guide 202
is 3 degrees, and the length of light guide 202 is 142 mm.
[0163] Diffusing unit 200 may also include a second light guide
(not shown) which receives diffused light 208 from the distal end
of light guide 202. This second light guide is sufficiently long so
that diffused light 208, which propagates from small angle diffuser
205, will be emitted from the entire surface of the exit plane of
the second light guide. The exit plane of the second light guide
therefore functions as an extended diffused source. For example, a
second light guide having a length of 50 mm and a small angle
diffuser which induces a a scattering angle of 10 degrees will
enable diffused light to span a diameter of greater than 5 mm at
the exit of the second light guide.
[0164] As shown in FIG. 9b, diffusing unit 200 comprises array of
microlenses 210, instead of an optic fiber as in FIG. 8a, which is
disposed adjacent to the proximate end of tapered light guide 202.
Array 210 is configured such that light rays 203 that exit
therefrom with half angle divergence A impinge the inner wall of
light guide 202.
[0165] FIG. 10 illustrates diffusing unit 700, which comprises
another type of angular beam expander, namely one which comprises a
set of concave and convex mirrors. Small angle fiber 701 from which
light rays 703 exit with a small half angle divergence A, such as 5
degrees, is advantageously employed since diffuser unit 700
provides a high angular amplification.
[0166] As shown in FIG. 10a, half angle divergence A is selected so
that a light ray 703 impinges on convex mirror 702 and is reflected
therefrom to concave mirror 705. A ray 703 is further reflected
from mirror 705 at an angle that enables it to impinge upon, and be
scattered by, diffusively transmitting element 710, which is
affixed to concave mirror 705. In FIG. 10b, diffuser unit 700 is
additionally provided with light guide 715. The light which exits
from diffusively transmitting element 710 is received by light
guide 715 and is reflected within its inner wall, resulting in wide
angle diffusing from the entire exit surface of light guide 715.
Light guide 715 therefore functions as an ideal extended diffused
light source.
[0167] FIG. 11 illustrates a diffuser unit in which two 40-45
degrees holographic diffusers 220 and 221 are attached to light
guides 222 and 223, respectively. Each holographic diffuser induces
a half angle divergence of approximately 45-50 degrees. In order to
increase the divergence, two holographic diffusers are used. Light
rays 218 propagating from a monochromatic light source are
scattered by diffuser 220 to a half angle of D and then are
reflected within the inner wall of light guide 222. The scattered
light rays are further scattered by diffuser 221 to a half angle of
E, are reflected within light guide 223, and exit the diffuser unit
at a half angle of F, which approaches 60 degree, the value
corresponding to an ideal transmitting diffuser. The light guides
are chilled so that the holographic diffusers, which are usually
made from plastic material, will also be chilled so that they will
be able to withstand the high thermal stress imposed by a high
power laser beam. Each light guide may be solid or hollow, and may
be made from glass, sapphire, a liquid dielectric, or plastic.
[0168] FIG. 12 illustrates another preferred embodiment of the
invention in which diffuser unit 300 comprises two distinct
diffusers 301 and 302, wherein at least one is axially
displaceable. FIG. 12a illustrates diffuser unit 300 in an active
position, such that diffusers 301 and 302 are essentially in
contact with each other. When in an active position, diffusers 301
and 302 act as a singular randomly scattering diffuser, since
substantially all of the monochromatic light 305 that impinges on
diffuser 301 is transmitted to diffuser 302. Although the energy
density needed for performing an efficacious treatment with
monochromatic light 305 is minimally affected, a slight increase of
the laser energy can compensate for any energy density losses. FIG.
12b illustrates diffuser unit 300 in an inactive position, such
that diffusers 301 and 302 are separated from each other by a
distance L, which is sufficiently long to ensure that the radiance
of the scattered light which exits diffuser 301 and is additionally
scattered by diffuser 302 is below a level that is safe to one's
eyes.
[0169] As shown, diffuser 301 is axially displaceable by means of a
plurality of springs 308 that connect diffuser mount 301a to
diffuser mount 302a. When lever 315, which is connected to diffuser
mount 301a, is depressed springs 308 are compressed and diffuser
301 becomes substantially in contact with diffuser 302, as shown in
FIG. 12a. Distal end 317 of handpiece 303 is then brought in
contact with a skin location to be treated by monochromatic light
305 having a high energy density and a high radiance. Upon
completion of a desired surgical or cosmetic procedure, lever 315
is released and springs 308 are biased to separate diffuser 301
from diffuser 302 by a distance of L, as shown in FIG. 12b, whereby
the radiance of the scattered light is below a safe level. It will
be appreciated that any other means well known to those skilled in
the art for axially displacing one or more of the diffusers may be
used.
[0170] FIG. 13 illustrates an embodiment of the present invention
by which tissue, having a larger surface area than the area of the
beam impinging thereon, may be treated without overexposure to a
laser beam. In prior art systems using a scanner, the treatment
beam is quickly displaced in a programmable fashion from one
location to another on the tissue to be treated. Although this
method provides rapid and reliable treatment, there is a
significant risk, however, that the laser beam is liable to be
aimed at eyes, skin or flammable materials located in the vicinity
of the laser unit.
[0171] The diffusing unit generally designated by 60 is shown. In
this embodiment the diffusing unit is rigidly attached to delivery
system 61, which is provided with a scanner. Diffusively
transmitting element 63 is formed with a plurality of visible
targets 66 and is placed close to the skin, facing the distal end
of delivery system 61. Diffusing unit 60 is preferably provided
with a clear transmitting element, as described hereinabove.
Coherent collimated or convergent exit beam 64 is directed via a
plurality of repositionable reflectors 65 to a predetermined target
66 graphically indicated on diffusively transmitting element 63.
The beam that impinges upon a predetermined target 66 is randomly
scattered and converted into non-coherent beam 67 whose energy
density is essentially similar to that of exit beam 64. Reflectors
65 are controllably repositionable by means of a scanner, whereby
they may be displaced from one position and angular disposition to
another, so as to accurately direct exit beam 64 to another target
66. The sequence of which target is to receive exit beam 64 after a
selected target is programmable and is preferably semi-random to
reduce pain which may be felt resulting from the treatment of two
adjacent targets, with the time increment between two doses of
laser treatment being less that less than a preferred value. A
programmable sequence precludes on one hand the chance of a target
not to receive an exit beam at all, and on the other hand precludes
the chance of not to be inadvertently exposed twice to the exit
beam. With the usage of diffusing unit 60, small-diameter beams,
e.g. 0.1-7.0 mm, may be advantageously employed to treat a tissue
having an area of 16 cm.sup.2. Similarly, a scanner may be employed
for any other feasible wide-area diffusing unit, such as an array
of diffusers/light guides incorporating those units illustrated in
FIGS. 9-12, whereby an exit laser beam may be directed to each of
the diffusers/light guides. Such an array may consist of 9
diffuser/light guides, each having a 3-mm diameter, to -cover an
area of 81 mm.sup.2. Scanning may also be achieved by laterally
moving an angular expander over the diffuser/light guide array.
[0172] FIG. 14 illustrates another preferred embodiment of the
invention in which a diffusing unit is not used, but rather a
diverging optical element is employed to produce an exit beam
having radiance, or alternatively, energy density, depending on the
wavelength, below a safe level.
[0173] As shown in FIG. 14a, diverging optical element 741 is
placed in diverging unit 748, which is attached to the distal end
of the laser unit by any means depicted hereinabove in FIG. 2.
Divergent element 741, which is provided with a relatively short
focal length, focuses input beam 740 at point F. The beam diverges
at a point distally located with respect to point F, as well known
to those skilled in the art, and produces divergent beam 742 having
a divergent angle of H, a cross section 743 at a plane coplanar
with distal end 744 of diverging unit 748 and a cross section 752
at a plane coplanar with shield 750. When divergent beam 742 has a
cross sectional dimension at least equal to cross section 752, its
radiance is less than an eye safe level.
[0174] Pulsed laser radiation in the wavelength range of 1400 nm to
13 microns, according to the ANSI Z 136.1 standard, is considered
eye safe if the Accessible Energy Limit (AEL) at the ocular plane
is less than a value of 0.56*t**(1/4) J/cm.sup.2, where t is the
pulse duration in seconds. For example, a typical pulse duration
ranging from 1 to 100 msec is associated with an AEL ranging from
0.1 to 0.3 J/cm.sup.2, respectively. Accordingly, diverging unit
748 is provided with at least one shield 750, each of which
prevents one's head from entering a zone of the divergent beam at
which the energy density is greater than the AEL. Shield 750 is
connected to tube 746 of diverging unit 748 by means of rigid
member 747, and cross member 749. The length of cross member 749
and the degree of angular divergence H is selected to ensure that
the energy density distal to shield 750 is less than the AEL.
Normally, cross member 747 is unyielding to head pressure, thereby
ensuring eye safety. However, when a lever is actuated, for
example, cross member 747 is opened and a spring (not shown), which
is normally in a relaxed state and connected to both rigid member
747 and cross member 749, becomes tensed and allows the shield to
be proximately displaced. When shield 750 is proximately displaced,
distal end 744 of diverging unit 748 may be in contact with a
target skin location and cross section 743 of beam 742 having a
sufficiently high energy density for a desired application may be
utilized. For example, diverging unit 748 is suitable for those
applications by which a laser beam is greatly absorbed by
water.
[0175] FIG. 14b illustrates diverging unit 950, which comprises
array 991 of focusing lenslets each of which has a diameter of e.g.
0.7 mm, array 992 of lenses each of which is provided with
reflective coating 993 on its distal side, and a plurality of
convex reflectors 995 attached to transparent plate 994. Rays 990
from a collimated laser beam are focused by lenslets 991 and
transmitted through non-reflective area 999 formed on the distal
side of each lens 992. The location of each non-reflective area 999
is selected so that a focused ray propagating therethrough will
impinge upon a corresponding reflector 995 at such a reflecting
angle such that it will be reflected therefrom and strike a
corresponding reflective coating 993, from which it is again
reflected and propagates through transparent plate 994. Most rays,
such as ray 996 then exit plate 994. However, some rays, such as
ray 989, strike a transversal side 997 of plate 994, which is
provided with a reflective coating and causes these rays to exit
plate 994. Plate 994 accordingly functions as a light guide when
transversally reflecting light rays strike a side 997. The length,
i.e. the distance between sides 997, of plate 994 is substantially
equal to the length of array 991, and therefore the energy density
of an input beam is preserved at the exit of plate 994. In order to
comply with the requirements of the aforementioned standards,
namely to achieve a safe radiance level with a lens having a
diameter of 0.7 mm and producing a divergent half angle of 60
degrees, a lenslet 991 with a focal length of 3 mm may be used to
achieve a uniform radiance at a solid angle of approximately .PI.
steradians.
[0176] The distal end of plate 994 may be etched to further diffuse
the divergent light exiting therefrom, so that the distal end may
function as an extended diffused light source. If desired, the
transparent plate may be substituted by a light guide.
[0177] In summation, the present invention incorporates four groups
of units which cause a monochromatic light to diverge at a
sufficiently wide angle so that the radiance of an exit beam is eye
safe: [0178] 1) A diverging unit provided with a single diverging
optical element; [0179] 2) A multi-component diverging unit
provided with reflective and refractive optical elements, and
without any diffusers; [0180] 3) A diffusing unit provided with a
single thin diffusively transmitting element; and [0181] 4) A
multi-component diffusing unit, whereby a wide divergent, diffusing
angle is achieved by using a high thermally resistant
refractive/reflective optical component, as well as at least one
thermally resistant low angle diffuser.
[0182] When a multi-component diffusing or diverging unit is
employed, a relatively simple eye safety monitoring device can be
used. Due to the high thermal durability of the selected
multi-component unit, the radiance homogeneity is essentially
preserved from the proximate end to the distal end thereof.
Consequently, limited sampling of the radiance level is required,
and an expensive monitoring device is rendered unnecessary. Another
advantage of a multi-component unit is that monochromatic light
reflected from the skin returns to the corresponding unit via a
light guide with respect to a diffusing unit and via a transparent
plate with respect to a diverging unit, preventing an adverse
effect to the skin if reflected monochromatic light were to return
thereto.
[0183] FIG. 15 illustrates another preferred embodiment of the
invention in which a diffusing unit is provided with a skin cooling
system. Transparent skin cooling devices are often used in
conjunction with skin laser treatments. However they do not scatter
laser light and do not reduce the risks associated with exposure to
a laser beam. FIGS. 13a-d illustrate prior art skin coolers. In
FIGS. 15a and 15b transparent lenses or plates 80 are in contact
with tissue 79. Cooling liquid 81, which flows through conduit 83,
conducts heat from the heated skin to a cooler. Treatment laser
beam 82 propagates without being scattered through the cooling
device and penetrates the skin. In FIG. 15c gaseous coolant 84 is
used. In FIG. 15d, highly conductive plate 86 is in contact with
tissue 79 and chilled by thermoelectric cooler 85.
[0184] As shown in FIG. 15e, diffusing unit 75 comprises
diffusively transmitting element 74, clear transmitting element 70
and conduit 71 formed therebetween. Conduit 71 is filled with a low
temperature gas or liquid of approximately 4.degree. C., which
enters conduit 71 through opening 72 and exits at opening 73 The
cooling fluid preferably flows through a cooler (not shown).
Diffusing unit 75 is positioned in contact with the skin, for
treatment and cooling thereof. Clear transmitting element 70 is
preferably produced from a material with a high thermal
conductivity such as sapphire, in order to maximize cooling of the
epidermis. Diffusively transmitting element 74 is disposed such
that its proximal face is frosted side and its distal face is
planar, facing conduit 71. In FIG. 15f, the diffusing unit
comprises diffusively transmitting element 74 made from sapphire,
which is chilled at its lateral sides 75 by thermoelectric cooler
76. The proximal side of 74 is frosted and the smooth distal side
faces the skin. The parameters of the flowing fluid and of the
cooler are similar, by example, to the Cryo 5 skin chiller produced
by Zimmer, California, USA. It will be appreciated that any of the
skin cooling means illustrated in FIGS. 15d-f may be used to cool
skin which is heated as a result of the impingement of
monochromatic light thereon even though a diffusively transmitting
element is not used.
[0185] The eye safety when exposed to the exit beam of a diffusing
or diverging unit is significantly improved relative to prior art
devices.
[0186] Parameters for eye safety analysis are presented in "Laser
Safety Handbook," Mallow and Chabot, 1978 in which the standard
ANSI Z 136.1 is cited. A laser beam which is reflected from a light
diffusing surface is categorized as an extended diffused source if
it may be viewed at a direct viewing angle A, greater than a
minimum angle Amin, with respect to a direction perpendicular to
the source of the laser beam. If a reflected beam may not be viewed
at angle A, it is categorized as an intrabeam viewing source. Since
a reflected beam is more collimated when viewed at a distance,
viewing conditions are intrabeam if the distance R from the source
of the laser is greater than a distance Rmax.
[0187] Another significant parameter is the maximum permitted
radiance, normally referred to as Accessible Energy Limit (AEL)
while staring at a diffusing surface which completely reflects a
laser beam. AEL depends on the energy density, exposure duration,
and wavelength of the laser beam,. as well as the solid angle into
which the laser beam is diffused. The safety level of a laser unit
is evaluated by comparing the AEL to the actual radiace (AR) of the
laser beam. Staring at the exit of a diffusing unit according to
the present invention is equivalent to staring at a reflecting
extended diffuser with 100% reflectivity. The AEL for visible and
near infrared radiation exiting a diffusing unit for which
protective eyeglasses are unnecessary based on an extended diffuser
source is defined by ANSI Z 136.1, as 10*k1*k2*(t 1/3)
J/cm.sup.2/sr, where t is in seconds and k1=k2=1 for a wavelength
of 400-700 nm, k1=1.25 and k2=1 at 750 nm, k1=1.6 and k2=1 at 810
nm, k1=3 and k2=1 at 940 nm and k1=5 and k2=1 at a wavelength of
1060 to 1400 nm. The safety limit set by ISO 15004: 1997E for
pulsed radiation is 14 J/cm.sup.2/sr.
[0188] The actual radiance (AR) is the actual energy per cm.sup.2
per steradian emitted from a diffusing unit. The ratio between AEL
and AR indicates the safety level of the laser unit employing a
diffusing unit, according to the present invention. A ratio less
than 1 is essentially unsafe. A ratio between 1.0 and 5 is similar
to that of high intensity flashlight sources used in professional
photography and intense pulsed light sources used in aesthetic
treatments, and is much safer than prior art laser sources. Prior
art laser sources which do not incorporate a diffusing unit have a
ratio which is several orders of magnitudes less than 1.
[0189] Table I below presents a comparison in terms of eye safety
between the exit beam of monochromatic light after being scattered
by a diffusing unit into a solid angle of 3.14 sr, which is
equivalent to that attained by an ideal transmitting diffuser,
according to the present invention. The parameters for a
non-coherent diode-based laser unit are based on one produced by
Dornier Germany. The parameters for a non-coherent
Alexandrite-based laser unit are based on one produced by
Sharplan/ESC (Epitouch). The parameters for a non-coherent
Nd:YAG-based laser unit intended for hair removal are based on one
produced by Altus,USA. The parameters for a non-coherent
Nd:YAG-based laser unit intended for photo-rejuvenation are based
on one produced by Cooltouch, USA The parameters for a non-coherent
dye-based laser unit are based on one produced by ICN (Nlight). The
parameters for an intense pulsed light laser unit are based on one
produced by ESC. The AEL for a particular wavelength and pulse
duration is based on the aforementioned ANSI Z 136.1 standard.
TABLE-US-00001 TABLE I Non coherent CW Diode Non coherent Non
coherent Nd: YAG Non coherent 60 degrees Non coherent Alexandrite
Nd: YAG based Dye based Intense Pulsed diffuser System type Diode
based based based Photo- Photo- Light Tooth Application Hair
removal Hair removal Hair removal rejuvenation rejuvenation Hair
removal whitening Parameters Wavelength 940 nm 755 nm 1064 nm 1320
nm 585 nm 645-900 nm 980 nm Energy 6 J 10 J 11.3 J 7 J 0.6 J 90 J
1.5 J Pulse duration 50 msec 40 msec 60 msec 60 msec 0.5 msec 40
msec 1 sec Spot size 5 mm 7 mm 6 mm 6 mm 5 mm 10 .times. 30
mm.sup.2 5 .times. 5 mm.sup.2 Energy density 30 J/cm.sup.2 25
J/cm.sup.2 40 J/cm.sup.2 25 J/cm.sup.2 3 J/cm.sup.2 30 J/cm.sup.2 6
J/cm.sup.2 Extended view parameters A min 8 mrad 3.5 mrad 4 mrad 4
mrad 2.5 mrad 5 mrad 15 mrad R max 0.4 m 2 m 2 m 2 m 1.3 m 4 m 0.33
m Eye safety Parameters AEL/sr 11 J/cm.sup.2/sr 4.3 J/cm.sup.2/sr
19.5 J/cm.sup.2/sr 20 J/cm.sup.2/sr 0.79 J/cm.sup.2/sr 3.4
J/cm.sup.2/sr 35 J/cm.sup.2/sr AR/sr 9.6 J/cm.sup.2/sr 8
J/cm.sup.2/sr 12.7 J/cm.sup.2/sr 8 J/cm.sup.2/sr 0.79 J/cm.sup.2/sr
9.5 J/cm.sup.2/sr 8 J/cm.sup.2/sr Eye safety Figure of merit AEL/AR
1.14 0.53 1.54 2.5 1 0.35 4.1
[0190] The table shows that the exit beam according to the present
invention is essentially as eye-safe, or safer than, broad band
non-coherent intense pulsed light sources, such as those used for
professional photography or those used for cosmetic surgery. The
scattered monochromatic light, for most of the light sources, does
not necessitate protective eyeglasses and is safer than an
accidental glance into the sun for a fraction of a second. Although
the ratio for the Alexandrite and Intense Pulsed Light sources is
less than 1 and protective eyeglasses must be worn, the required
optical attenuation for these light sources is less than 3, much
less than the required optical attenuation with the use of a
conventional monochromatic light source not provided with a
diffusing unit, which is on the order of 10.sup.4-10.sup.7. It will
be appreciated that a similar level of eye safety for laser units
utilizing a diffusing unit may be achieved with a very wide
scattering angle, approaching a half angle of 60 degrees or a solid
angle of .PI. steradians. Small angle scattering may result in a
different level of eye safety when operated at an energy density
suitable for aesthetic treatments; nevertheless, such a scattered
exit beam is much safer than the exit beam of a conventional
coherent laser unit.
[0191] The radiance of the light emitted by a diffusing unit can be
measured to verify that it is in compliance with the appropriate
standards for laser eye safety. In one embodiment, a converted
laser utilizing a diffusing unit in accordance with the present
invention is provided with an eye safety measurement device. Such a
device may be an energy meter such as that produced by Ophir, USA
or an array of light detectors 805 as depicted in FIG. 16. The eye
safety measurement device is provided with control circuitry which
is in communication with the operating system of the laser unit, so
that, as a result of a mishap, a warning is issued indicating that
protective eyeglasses are required if the measured radiance of a
scattered laser beam is greater than a predetermined safe value.
Alternatively, the control circuitry may discontinue operation of
the laser unit if the measured radiance of a scattered laser beam
is greater than a predetermined safe value.
[0192] FIG. 16 illustrates an exemplary eye safety measurement
device, designated as numeral 800. Device 800 is operative to
measure the radiance of scattered light 810, which is scattered by
means of diffusing unit 15 attached to distal end 809 of laser unit
handpiece 801. Device 800 is provided with an array of light
detectors 806, e.g. complementary metal oxide semiconductor (CMOS)
detectors which provide light imaging, at distal end 805 thereof,
on which scattered light 810 impinges after passing through
aperture 808 of diameter Q.sub.0 and lens 807. After distal end 809
is inserted into a complementary opening formed within device 800
until contacting annular abutment plate 804 perpendicular to outer
wall 803 of device 800, the laser unit is fired. For purposes of
clarity, light which propagates therough segment Q.sub.1 of
diffusing unit 15 impinges on segment Q.sub.2 of detector array
806. The radiance of scattered light 810 therefore is determined by
dividing the amount of energy sensed by detectors 806 by diameter
Q.sub.0 of aperture 808 and by the solid angle characteristic of
the detector structure. For example, the distance D between
abutment plate 804 and aperture 808 is 200 mm, segment Q.sub.1 of
the diffusing element 15 is 0.7 mm, and diameter Q.sub.0 of the
aperture is 7 mm, to comply with the regulations set forth in ANSI
Z 136.1.
[0193] FIG. 17 illustrates another embodiment of the invention,
wherein eye safety in the vicinity of a laser unit that emits an
infrared beam or other invisible radiation is increased by adding a
flashing device to the laser system to cause one's eyes to blink
during the propagation of the laser beam.
[0194] FIG. 17a illustrates distal end 960 of a laser unit, which
emits light 955 generated therefrom, preferably being scattered
monochromatic light when a diffusing unit is employed. To prevent
damage to eye 962 of a bystander located in the vicinity of the
laser unit, flashing device 961 is added to distal end 960.
Flashing device 961 generates a short visible light flash a
fraction of a second prior to the firing of a laser beam.
[0195] As shown in FIG. 17b, activation of the laser unit initiates
an electrical pulse 963 at time t.sub.0, which triggers a timer
circuit (not shown). The timing circuit is adapted to generate and
transmit pulse 964 at time t.sub.1 to flashing device 961, to
produce a flash is sensed by eye 962. Flashing device 961 may be a
well known flashing means associated with cameras or may utilize
diodes, or any other feasible means to produce an instantaneous
flash. After a predetermined period of time, the timing circuit
transmits a pulse to the control system of the laser unit to fire a
laser beam at time t.sub.2. This predetermined period of time,
namely the difference between t.sub.2 and t.sub.1, is approximately
0.25 seconds, equal to the reaction time of uncontrolled blinking
as a response to light, and is preferably no more than 0.20
seconds. A flashing device 961 may be added to any source of
monochromatic light, such as any type of laser or IPL sources,
whether producing visible or invisible light.
[0196] FIG. 17c illustrates another application of flashing device
961. By generating a flash with device 961 and determining whether
detector 975 senses light retroreflected from eye 962, a
microprocessor (not shown) in communication with a control circuit
(not shown) and with detector 975, e.g. a photodetector, can
determine that eye 962 is in danger of being injured from the
imminent firing of a laser beam from the laser unit. The choroid
layer of the retina diffusely reflects light source 973 that
impinges thereon from the previously generated flash, and the
optics of eye 962 re-image, or retroreflect, the light back to
flashing device 961. Retroreflected beam 974 is reflected from beam
splitter 970 through a lens (not shown) onto 975. Two additional
adjacent detectors (not shown) detect light reflected from other
areas in the room in which the laser unit is disposed. If the
signal generated by detector 975 has a much larger amplitude than
the signals generated by the additional detectors, the
microprocessor determines that eye 962 is in firing range of a
laser beam. The control circuit of flashing device 961 then sends a
disabling signal to the control system of the laser unit to thereby
prevent firing of a laser unit. When detector 975 is used to detect
a retroflected beam, and a flash is generated within the
predetermined time before the firing of a laser beam, as
illustrated in FIG. 17b, in order to cause uncontrollable blinking
of the eye during propagation of the beam, the laser unit is
inherently fail-safe. That is to say, even if the eye does not
blink, detector 975 will determine that eye 962 is in firing range
of a laser beam and the laser unit will cease operation.
[0197] As can be seen from the above description, a
diffusing/diverging unit of the present invention, which is mounted
to the exit aperture of a conventional laser unit, induces the exit
beam to be divergent/ and or scattered at a wide angle. As a result
the exit beam is not injurious to the eyes and skin of observers,
as well as to objects located in the vicinity of the target.
Nevertheless, the exit beam generally retains a similar level of
energy density as the beam generated from the exit aperture when
the diffusing unit is very close or essentially in contact with the
target, and is therefore capable of performing various types of
treatment, both for cosmetic surgery and for industrial
applications. Protective eyeglasses are generally not needed, and
if they are needed, conventional sunglasses would be the only
requirement, thereby allowing work in an aesthetic clinic to be
less cumbersome.
EXAMPLE 1
[0198] An experiment was performed to demonstrate the operating
principles of the present invention in which transparent light
diffusing adhesive "Magic Tape," manufactured by 3M, having a
thickness of 100 microns was attached to the distal end of an
Alexandrite laser unit having a diameter of 8 mm. The energy level
of the laser beam is 11 J/pulse. The laser beam was directed to the
white (rear) side of a black developed photographic paper having a
thickness of 300 microns. For comparison, the laser beam was also
directed to the photographic paper without the use of the adhesive
tape.
[0199] The ablation of the black paper after the beam had
propagated and scattered through the white paper provides a visual
simulation of the capability of the laser beam to penetrate
transparent light-scattering skin in order to treat black hair
follicles (or any other type of lesion) under the skin.
[0200] The energy of the laser beam transmitted through the
adhesive tape, which caused the laser beam to scatter, was measured
by directing the beam to an energy meter located at a distance of 1
mm from the distal end of the laser unit. The energy of the
scattered laser beam dropped from 11 to 10 J. The results of this
experiment indicate that the diffusively transmitting element did
not absorb a significant amount of energy, since a loss of 10% is
expected in any case due to Fresnel reflection.
[0201] When the laser beam was directed to the white (rear) side of
a developed photographic plate at a distance of 1 mm, an ablation
of the black color on the opposite side of the photographic paper
resulted. There was no difference in the results between usage of
light diffusing tape or not. This experiment demonstrates that the
performance of a non-coherent Alexandrite laser beam, according to
the present invention, at a distance of 1 mm is essentially equal
to the corresponding coherent laser beam.
[0202] When the laser beam was directed, without the addition of
light diffusing tape, at the photographic paper from a distance of
at least 8 mm, an ablation resulted that is identical to that which
was generated from a short distance of 1 mm. However, when light
diffusing tape was applied to the exit aperture of the laser unit
from a distance of at least 8 mm, the scattered beam did not result
in an ablation. Accordingly, the present invention allows for a
high level of safety and lack of damage to bodily tissue when
disposed at a relatively large distance therefrom.
EXAMPLE 2
[0203] In a second experiment a long pulse Alexandrite laser unit
having a wavelength of 755 nm, pulse duration of 40 msec, and
having an energy density of 25 J/cm.sup.2 was used for hair
removal. A diffusing unit with an ultra-densely woven polymer-based
diffuser having a half angle of 15 degree produced by Barkan or a
holographic diffuser produced by Physical Optics Corporation (USA)
having a half angle of 40 degrees was employed. The diffusers were
used in a one-time basis. Chilling gel was applied between the
diffuser and the skin.
[0204] Each pulse of a laser beam scattered by a diffusing unit
formed a spot of 5.5 mm on various skin locations including arms,
bikini lines and armpits of 10 patients. Full hair removal was
noticeable immediately after the firing of the laser beam. Each
spot was compared to a control area with an identical diameter
formed by an unscattered laser beam generated by the same laser
unit with similar parameters, and similar results were achieved.
Hair did not return to those spots for a period of one month.
EXAMPLE 3
[0205] A long pulse Alexandrite laser unit having a wavelength of
755 nm, pulse duration of 40 msec, and having an energy level of
1-20 J is suitable for hair removal.
[0206] The diameter of the diffusing unit is 7 mm, and its
scattering half angle is 60 degrees. A diffusing. unit comprising a
diffuser with a small scattering angle, a highly divergent lens and
a light guide is added to the distal end of the laser unit.
[0207] The prior art energy density of 10-50 J/cm.sup.2 is not
significantly reduced with the employment of a diffusing unit. The
laser unit operates at 25 J/cm.sup.2 and generates a radiance of 8
J/cm.sup.2/sr. Since the acceptable radiance limit according to
ANSI Z 136.1 is 4.3 J/cm.sup.2/sr, bystanders are required to use
protective eyeglasses with 50% optical attenuation, an attenuation
similar to that of sunglasses and an order of 100,000 less than
typical protective eyeglasses worn during operation of a laser
unit. For a larger target area, a scanner such as the Epitouch
model manufactured by Lumenis may be used.
[0208] A diffusing unit having a diameter of up to 7 mm is
particularly suitable for lower energy lasers, which are relatively
small, remove hair at a slower speed from limited area and are
inexpensive. An application of such a laser, when employed with a
diffusing unit, includes the removal of eyebrows.
EXAMPLE 4
[0209] A pulsed ND:YAG laser unit such as one produced by Altus
(USA) or Deka (Italy) having a wavelength of 1064 nm, pulse
duration of 100 msec, and having an energy level of 0.5-60 J is
suitable for hair removal at an energy density ranging from 35-60
J/cm.sup.2.
[0210] A diverging unit with an array of focusing lenslets, an
array of lenses provided with reflective coating on its distal
side, and a plurality of convex reflectors attached to a
transparent plate is used, such that the diverging half angle is
close to 60 degrees. When a laser beam having an energy density of
40 J/cm.sup.2 is generated, a radiance of 12.7 J/cm.sup.2/sr at the
exit of the diverging unit is induced, approximately half of the
maximal permitted radiance according to ANSI Z 136.1.
EXAMPLE 5
[0211] A long pulse diode laser unit having a wavelength ranging
from 810-830 nm, or of 910 nm or 940 nmpulse duration ranging from
1-200 msec, and having an energy level of 0.5-30 J is suitable for
hair removal at an energy density ranging from 20-50
J/cm.sup.2.
[0212] The diameter of the treated area, or spot size, ranges from
1-20 mm. The diffusively transmitting element is preferably made
from fused silica, sapphire, or is a holographic diffuser used in
conjunction with a light guide or with any other diffusing unit
described hereinabove. The scattering half angle is close to 60
degrees. A scanner may be integrated with the diffusing unit. The
delivery system to which the diffusing unit is attached may be a
conical light guide, such as that manufactured by Coherent or
Lumenis, a guide tube produced e.g. by Diomed or a scanner produced
e.g. by Assa. With a diffusing unit having a diameter of 5 mm and a
laser beam generated with an energy density of 20 J/cm.sup.2 and a
pulse duration of 100 msec, the radiance at the exit of the
diffusing unit is 9.6 J/cm.sup.2/sr, lower than the maximal
permitted radiance value of 11.0 J/cm.sup.2/sr.
EXAMPLE 6
[0213] A miniature diode laser unit for home use operating at a
wavelength of approximately 810 nm, or 940 nm, such as one produced
by Dornier, Germany, and having a power level of 4 W is suitable
for hair removal. The invention converts a continuous working diode
laser unit, which is in a high safety class and usually limits
operation to the medical staff, into a lower safety class, similar
to non-coherent lamps of the same power level.
[0214] The diffusing unit utilizes an angular beam expander with a
convex reflector, a concave reflector having an inner diameter of
16 mm, a 10-degree glass diffuser, and a light guide having a
length of 20 mm and an inner diameter of 2 mm. The diameter of the
treated area, or spot size, is approximately 2 mm. The energy
density at the exit of the light guide is 30 J/cm.sup.2 and the
radiance thereat is approximately 10 J/cm.sup.2/sr. A scanner may
be integrated with the diffusing unit. The diode laser may also be
used without a scanner, in which case the laser will be pulsed for
a duration of approximately 300 msec.
EXAMPLE 7
[0215] A Ruby laser unit having a wavelength of 694 nm, pulse
duration ranging from 0.5-30 msec, and having an energy level of
0.2-20 J is suitable for hair removal.
[0216] The diameter of the treated area, or spot size, ranges from
1-20 mm. The larger spot sizes can be generated by Ruby lasers
manufactured by Palomar, ESC and Carl Basel, which provide an
energy density ranging from 10-50 J/cm.sup.2. The smaller spot
sizes can be generated by inexpensive low energy lasers, which are
suitable for non-medical personnel. A multi- component diffusing or
diverging unit may be used. The laser unit is much safer than a
conventional laser unit
[0217] A scanner, such as manufactured by Assa of Denmark or by
ESC, may. be used to displace a reflected collimated beam from one
aperture to another formed within the diffusing or diverging unit.
The scanning rate is variable, and the dwelling time at each
location ranges from 20-300 msec.
EXAMPLE 8
[0218] High risk laser units, such as Nd:YAG having a wavelength of
1.32 microns and manufactured by Cooltouch with a pulse duration of
up to 40 msec, a dye laser having a wavelength of 585 nm and
manufactured by N-Light/SLS/ICN, or a Nd:Glass laser having a
wavelength of 1.55 microns with a pulse duration of 30 millisec may
be used for non-ablative skin rejuvenation. This application is
aimed at the treatment of rosacea, mild pigmented lesions,
reduction of pore sizes in facial skin and mild improvement of fine
wrinkles, without affecting the epidermis. The advantage of these
lasers for non-ablative skin rejuvenation is related to. the short
learning curve and more predicted results due to the small number
of treatment parameters associated with the single wavelength. By
implementing a diffusing unit, the laser unit becomes safe and may
be operated by non-medical personnel.
[0219] An N-Light laser unit is initially operated at an energy
density of 2.5 J/cm.sup.2 for collagen contraction. The addition of
a diffusing unit makes the laser unit as safe as an IPL. The
addition of a multi-component diffusing or diverging unit with a
divergent half angle of 60 degrees and an exit diameter of 5 mm
results in a radiance level of 0.79 J/cm.sup.2/sr, which is equal
to maximal accepted limit.
[0220] A laser beam may be generated with a considerably less
expensive laser unit, having an energy level ranging from 0.5-3 J
and a slow repetition rate such as 1 pps, and generating a spot
size ranging from 2-4 mm. In the case of wrinkle removal, the
operator may follow the shape of the wrinkles with a small beam
size. Such a non-coherent laser beam having a beam size of 2-4 mm
is particularly suitable for aestheticians. Using a diffusing unit
depicted in FIG. 10b with a 10 degree diffuser and a light guide
having a length of 30 mm results in a laser unit with a radiance of
approximately 0.5 J/cm.sup.2/sr.
EXAMPLE 9
[0221] A pulsed Nd:YAG laser unit having a wavelength of 1064 nm
and manufactured by ESC and having an energy level of 0.5-60 J is
suitable for treatment of vascular lesions. The pulse duration
ranges from 1-200 msec, depending on the size of the vessels to be
coagulated (300 microns to 2 mm) and the depth thereof below the
surface of the skin. A LICAF (Litium Calcium Fluoride) laser unit
at a wavelength of 940 nm may also be advantageously used for this
application, and its associated laser beam is better absorbed by
blood than the Nd:YAG or Dye laser. A Dye laser at a wavelength of
585 nm and manufactured by Candela may be used to treat vessels
located at a low depth below the skin surface, such as those
observed in port wine stain, telangectasia and spider veins.
[0222] The diameter of the treated area, or spot size, ranges from
1-10 mm, depending on the energy level. A multi-component diffusing
or diverging unit is used, due to the relatively high energy
density of greater than 90 J/cm.sup.2 needed for the treatment of
deep vascular lesions. A scanner may be integrated with the
diffusing unit.
EXAMPLE 10
[0223] Q-Switch laser units having a pulse duration ranging from
10-100 nsec and having an energy density of 0.2-10 J/cm.sup.2 is
suitable for removal of pigmented spots, mostly on the face and
hands, as well as removal of a tattoos. A Q-switched Ruby laser as
manufactured by ESC or Spectrum, a Q-Switch Alexandrite laser
manufactured by Combio,and a Q-Switch Nd:YAG laser may be used for
such an application.
[0224] The diameter of the treated area, or spot size, ranges from
1-10 mm, depending on the energy level. A diffusing unit utilizing
two diffusively transmitting elements is used, wherein one is fixed
while the other is axially displaceable such that both elements are
essentially in contact with each other in an active position, e.g.
a gap of approximately 0.2 mm when a laser beam is fired. The gap
between the two elements is approximately 15 cm when the laser is
not fired. The diameter of the diffusing unit is 6 mm. Each
diffusively transmitting element is preferably made from glass,
sapphire or polymer.
[0225] The addition of such a diffusing unit with an axially
displaceable diffuser to the aforementioned laser units is
instrumental in rendering pigmented lesion and tattoo removal to be
a considerably less risky procedure. Tattoo removal is achieved
only by means of a laser beam, and is not attainable with intense
pulse light sources.
[0226] The removal of pigmented lesions may also be performed with
the use of an Erbium laser unit operated at a wavelength of 3
microns. Most pigmentation originates from the epidermis, and such
a laser beam penetrates only a few microns into the skin. With
implementation of a diffusing unit, this procedure may not
necessarily be performed by medical specialists. Aestheticians will
be able to treat a large number of patients, particularly since an
Erbium laser is relatively inexpensive.
[0227] Another application of the present invention involves the
field of dentistry, and relates to the treatment of pigmented
lesions found on the gums. Q-switched as well as Erbium lasers may
be used for this application.
EXAMPLE 11
[0228] A CO.sub.2 laser may be used for wrinkle removal. In prior
art devices, such a laser is used in two ways in order to remove
wrinkles: by ablation of a thin layer of tissue at an energy
density greater than 5 J/cm.sup.2 with a Coherent Ultrapulse, ESC
Silktouch, or Nidek Co.sub.2 laser and scanner for a duration less
than 1 msec; or by non-ablative heating of collagen in the skin for
lower energy densities, such as at 3 W, which may be achieved by
operation of a continuously working ESC derma-K laser for 50 msec
on a spot having a diameter of 3 mm.
[0229] With implementation of the present invention in which a
multi-component diffusing or diverging unit is attached to a
CO.sub.2 laser, a laser beam having a wavelength of 10.6 microns
may be generated. As opposed to other far infrared sources whose
thermal and spectrally broad bandwidth involves less control of
penetration depth, the interaction of a laser beam with tissue
according to the present invention is highly controllable and its
duration can be very short.
[0230] The diffusing and diverging units are preferably made from a
lenslet that is transparent to a CO.sub.2 laser beam such as ZnSe
or NaCL. The diameter of the diffusing unit ranges from 1-10 mm.
The divergent angle is greater than the minimal acceptable value so
as to produce a radiance level at the exit beam that is essentially
eye safe.
[0231] During ablation, a clear transmitting element of the
diffusing unit is separated from the tissue to be treated by a thin
spacer having a thickness of approximately 1 mm to allow for the
evacuation of vapors or smoke produced during the vaporization
process.
[0232] Similarly an Erbium laser unit operating at an energy
density above 2 J/cm.sup.2 and generating a laser beam greater than
3 microns may be used for wrinkle removal. Ablation is shallower
than attained with a CO.sub.2 laser and application of an Erbium
laser unit can be extended to tatto or permanent make up
removal.
EXAMPLE 12
[0233] A Nd:YAG or oyher laser unit may be used for treatment of
herpes. A diode laser with selective absorption of Cyanin green or
other materials by fatty lesions may be used for treatment of acne.
Both of these lasers may be used for treatment of hemorroids and
for podiatric lesions on the feet.
EXAMPLE 13
[0234] A dye laser unit operating at a wavelength of approximately
630 nm or 585 nm, or at other wavelengths which are absorbed by
natural porpherins present in P acne bacterias, such as produced by
Cynachore or SLS, as well as a laser unit operating at 1.45 microns
as produced by Candella, may treat acne lesions. The addition of a
diffusing or diverging unit to the laser unit may considerably
enhance eye safety and simplify the use of the laser unit for such
treatments by nurses and non-medical staff.
EXAMPLE 14
[0235] CO.sub.2, diode and ND:YAG laser units operating at an
average power of approximately 1-10 W are currently used by
physicians to treat pain. The addition of a diffusing unit may
enable the use of a highly safe device for that procedure in pain
clinics by non- medical personnel. Each laser unit may generate a
number of repetitively occurring sets of pulses, during a period of
approximately 3 seconds. The delivery system of the laser beam may
be an articulated arm or an optical fiber.
EXAMPLE 15
[0236] A diode laser unit manufactured by Candella (USA) generating
a laser beam with an energy density of 10 J/cm.sup.2, a wavelength
of 1445 nm, a pulse duration of 100 msec and a spot size of 3 mm is
suitable for non-ablative photorejuvenation.
[0237] A diverging unit with a single converging lens focuses the
beam to a focal zone 1.5 mm proximate to the distal end of the
diverging unit and and produces a half angle divergence of 45
degrees. The diverging unit is provided with a shield located 10 mm
distal to the focal point, whereat the energy density is reduced to
an eye safe level of 0.2 J/cm.sup.2 and a spot size is 23 mm.
EXAMPLE 16
[0238] It is advantageous to use an eye-safe laser unit for
welding. The employment of a diffusing unit is an excellent way to
reduce the risks associated with laser welding.
[0239] When welding thin transparent parts, such as those made from
plastic, e.g with a diode laser unit, it is often advantageous to
employ a large surface scanner or a large diameter beam which will
irradiate a large surface area and selectively activate all targets
with appropriate chromophores (by heat). Such a scanner is in
contrast to a scanner which is specifically targeted to the
geometrical locations at which welding materials are present. The
dwelling time of the welding laser beam at the targets depends on
the size of the welding element and the depth of material to be
melted. The dwelling time is also dependent on the size of a target
treated in photothermolysis. As an example, welding a strip having
a thickness of 50 micron to a substrate necessitates a dwelling
time of approximately 1 msec, while a strip having a thickness of
200 microns requires a dwelling time of 16 msec. The dwelling time
is proportional to the square of the thickness. Some welding
chromophores are transparent in the visible part of the spectrum,
but exhibit strong absorption in the near infrared part of the
spectrum.
EXAMPLE 17
[0240] Another industrial application for the present invention is
associated with microstructures to be evaporated. Paint stains or
ink may be selectively evaporated from surfaces such as clothes,
paper and other materials that need cleaning by use of various
pulsed lasers. One example of this application is related to the
restoration of valued antiques. Another example is the selective
vaporization of metallic conductors which are coated on materials
such as glass, ceramics or plastics. Vaporization of metallic
conductors can be achieved with a pulsed laser, which is generally
separated by a short distance from a target and whose beam has a
duration ranging from 10 nanoseconds to 10 milliseconds. Pulsed
Nd:YAG lasers are the most commonly used ablative industrial
lasers, although other lasers are in use as well. Pulsed Nd:YAG
industrial lasers may attain an energy level of 20 J concentrated
on a spot of 1 mm, equivalent to an energy density of 2000
J/cm.sup.2. The addition of a diffusing unit to an industrial laser
considerably increases the safety of the ablative device.
[0241] Pulsed Nd:YAG laser units are also suitable for improving
the external appearance of larger structures, such as the cleaning
of buildings, stones, antique sculptures and pottery. The laser
units in use today are extremely powerful, having a continuously
working power level of up to 1 kW, and are therefore extremely
risky. The addition of a diffusing unit considerably improves the
safety of these laser units.
[0242] A diffusing unit, when attached to an Excimer laser unit, is
suitable for photo-lithography, or for other applications which use
an Excimer laser unit for a short target distance.
[0243] With the addition of a multi-component diffusing or
diverging unit, all of these applications become much safer to a
user.
[0244] While some embodiments of the invention have been described
by way of illustration, it will be apparent that the invention can
be carried into practice with many modifications, variations and
adaptations, and with the use of numerous equivalents or
alternative solutions that are within the scope of persons skilled
in the art, without departing from the spirit of the invention or
exceeding the scope of the claims.
* * * * *