EYE SAFE DERMOTOLOGICAL PHOTOTHERAPY
Field of the Invention
The present invention is related to the field of intense pulsed light sources. More
particularly, the present invention is related to providing an eye-safe, intense
pulsed light source that is suitable for correcting aesthetic 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 an intense pulsed light source, by diverging the intense pulsed light 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
Intense Pulsed Light (IPL) sources are used for the treatment of a variety of
aesthetic skin problems, including hair removal, skin rejuvenation including
wrinkle removal, treatment of vascular lesions, treatment of acne, etc. Intense
pulsed light sources are broad band sources, such as Xenon flash lamps, spectrally
filtered to obtain narrower and more selective emission wavelengths. Typical
energy density levels utilized in hair removal are 5-50 J/cm2, with pulse durations ranging from approximately 3 to 300 msec. IPL sources are mostly operated in a
multiple pulse train mode such as a 50 msec pulse which consists of three pulses
of 3 msec each with a 20 msec delay between the pulses. The treatment area is
often close to 1 x 4 cm.
Such treatment is generally conducted by trained personnel, such as nurses under
the supervision of a physician. Aesthetic systems based on high intensity light are
divided into monochromatic pulsed laser sources, such as described in US Patent
No. 5,879,346 and non-coherent broad-band IPL sources, such as described in US
Patent Nos. 5,683,380, 5,885,273, 6,187,001, 6,280,438, 6,214,034, 5,964,749, and
6,387,089.
These prior art systems are extremely risky to the eyes and may cause blindness if
a bystander or a patient accidentally stares at the distal end of the treatment
system. As a result, the safety level of prior art laser and IPL sources utilized for
aesthetic treatments is such that protective eyeglasses are mandatory. The use of
both laser and IPL sources without supervision of a physician is prohibited in
many countries.
In addition to the accidental risk associated with directly staring at the distal end
of a pulsed light based treatment device without wearing protective eyeglasses,
there is a longer term risk associated with unavoidable staring at the treatment
site. The treated skin backscatters bright light which originates from the
treatment device, and the backscattered light repeatedly reaches the eyes of an
operator, causing severe eye fatigue .
The conversion of an IPL aesthetic source into an inherently eye-safe device which
does not require medically trained operators and which does not necessitate the
use of inconvenient protective eyeglasses would therefore be advantageous.
Protective eyeglasses, which are needed for the attenuation of backscattered
treatment light and should transmit ambient illuminating hght having a broad
band spectrum for adequate visibility, limit the field of view of an operator and are
opaque at a broad range of wavelengths, resulting in a darkened treatment site.
The need for protective eyeglasses during aesthetic treatments is obviated if the risks associated with direct staring at the distal end of an IPL source and with
skin backscattering are eliminated. Co-pending International Patent application
PCT/IL02/00635 by the same applicant, the description of which is incorporated
herein by reference, discloses a laser unit suitable for aesthetic treatment, which
is converted into an eye-safe laser unit.
One cause of eye risk associated with aesthetic treatments with a non-coherent
IPL source is the possibility of staring directly at the flash lamp through a light
guide (see Fig. 2). When a light guide is not employed, as described in U.S. Patent
No. 6,187,001, direct view is even more probable. The energy density emitted
directly from a flash lamp, e.g. having a size of 3 x 40 mm, may reach an energy
density level of 40-60 J/cm2 or higher. The flash lamp may be considered a diffused
light source which emits energy at a solid angle close to 3.14 steradians, achieved
by ideal diffuser sources with 100% transmission and provided with Lambertian
angular scattering properties. As a result, the radiance, i.e. the energy density per
solid angle, of the flash lamp is close to 15-20 J/cm2/steradian. In many cases
radiance may be even higher than that level.
The maximal permitted radiance or accessible emission limit (AEL) emitted from
an extended diffused light source used without protective eyeglasses is given in
the FDA eye safety standard 1040.10 21 CFR Ch.l and in the ANSI Z136.1
standard, and is a function of wavelength and pulse duration. If divided into
narrow spectral segments, the radiance for each spectral segment is given by the
equation:
AEL = 10 * kl *k2 * T A 1/3, where kl equals 1 in the visible part of the
spectrum, 1.6 at a wavelength of approximately 800 n , 3 at a wavelength of
approximately 980 nm and 5 at a wavelength of approximately 1064 nm, k2 =1,
and T is the pulse duration expressed in seconds.
Most intense pulsed light sources operate in spectral bands having a lower limit of
approximately 585 nm (kl=l) or 645 nm wavelength (kl =1) for photorejuvenation
and 755 nm (kl=1.3) or 810 wavelength (kl=1.6) for hair removal. The energy
content at a higher wavelength is smaller. As a result, the maximal permitted
radiance from IPL sources approximates AEL = 10 * 1.5 * T Λl/3. For a pulse
duration of 3 msec often used for photorejuvenation, which is strongly based on
absorption of light in extremely thin vessels with a thermal relaxation time of less
than 1 msec, the AEL is approximately 3 J/cm2/sr, a value much less than the
radiance emitted by a flash lamp of 15-20 J/cm2/sr, as referred to hereinbefore. An
IPL source used with high efficacy in aesthetic treatments is therefore not eye-
safe and emits a radiance which may be 6-13 times above the safe limit set by the
aforementioned FDA standard. It will be appreciated that even a factor of 2 above
the accepted standard for eye safety requires the use of inconvenient protective
glasses during an aesthetic treatment.
It will be appreciated that there is a trade off between the efficacy of an intense
light source used in aesthetic treatments and the corresponding eye or skin safety.
As the efficacy is higher, the energy density is higher, and therefore there is a higher risk of burning the skin since such an intense light source is in contact
with the skin. To prevent skin burning, some prior art intense light sources are
provided with a chiller, which chills the skin just before firing the IPL.
Although a variety of IPL sources are used in the treatment of aesthetic skin
disorders such as devices produced by LUMENIS USA (Epilight, Quantum),
RADIANCY, PALOMAR (USA), DEKA (ITALY), SYNERON (Israel), and the
fluorescent frequency-shifted PLASMALITE™ (USA, SWEDEN), they all suffer
from the high risk associated with the existence of a direct line of sight between a
flash lamp and the eye. Furthermore, prior art aesthetic systems which utilize
high energy, short pulse duration flash lamps for hair removal, wrinkle removal,
skin rejuvenation or the treatment of acne, lack protective measures, such as a
light diffuser placed within the line of sight between the flash lamp and skin,
which would obviate the use of protective eyeglasses during the treatment.
As mentioned above, in order to completely eliminate the necessity of wearing
inconvenient protective eyeglasses during aesthetic treatments with IPL sources,
the amount of backscattered treatment light which reaches the eyes should also be
reduced .
Protective eyeglasses used in conjunction with IPL sources, such as those
produced by Glendale USA, Laser-R Shield USA, Bolle, France, or Yamamoto,
Japan are generally based on selective absorption of light by an optical filter.
Since the protective eyeglasses used to reduce broad band radiation associated
with IPL sources are dark, the visibility of the treatment site, which is usually
illuminated by broad band radiation, is similarly reduced. Other protective
eyeglasses, such as those disclosed in US Patents Nos. 4,462,661, 5,671,035,
5,022,742, 5,841,507, 5,519,522, 4,968,127, 5,208,688 and 6,170,947, are based on
the attenuation of light by liquid crystal devices. These prior art devices are
relatively heavy and cumbersome, and limit the field of view of an operator.
Additional aesthetic systems related to the current invention are devices
incorporating both IPL and laser sources in a single system. For example, a
"Quantum" system produced by LUMENIS incorporates a spectrally broad-band, non-coherent IPL source for hair removal or photorejuvenation and a
monochromatic coherent Nd.YAG pulsed laser operated at 1064 nm for the
treatment of leg veins. Coherent laser sources, like all prior art aesthetic lasers,
are extremely risky to the eyes, having a radiance which is often more than 10,000 times above the AEL .
Other relevant prior art is disclosed in US Patent 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.
If the eye safety level of a laser and of an IPL source were reduced to a level below
that listed in the aforementioned standards, such a device would be able to be
operated by personnel without any medical background, such as aestheticians,
and also by individual users at home.
Prior art IPL sources used for aesthetic treatments are incapable of generating
non-coherent light at both a high enough energy density, which would assure
treatment efficacy, and at a low enough radiance, which would not present a risk
of injury to the eyes of bystanders .
It is an object of the present invention to provide a non-coherent IPL source that
may be used for aesthetic procedures.
It is an object of the present invention to provide a non-coherent IPL source that
overcomes the disadvantages of the prior art.
It is another object of the present invention to provide an IPL source that is not
injurious to the eyes of an operator or of an observer located in the vicinity of, or at
a distance from, a target.
It is yet another object of the present invention to provide an IPL source which
does not necessitate the use of protective eyeglasses, without causing severe eye
fatigue.
It is yet another object of the present invention to provide an IPL source which
could be operated by personnel without any medical background.
Other objects and advantages of the invention will become apparent as the
description proceeds.
Summary of the Invention
The present invention comprises a method of improving bodily safety of
bystanders exposed to an intense pulsed light directed to a target, comprising: providing a source for generating intense pulsed light, causing said source to
generate at least one pulse of polychromatic light, directing said pulsed light to a
target, and diverging said pulsed light at a diverging location between said source
and said target, whereby the energy density of light exiting from said diverging
location is substantially equal to the energy density of the intense pulsed light,
and at a distance from said diverging location the radiance of said exiting light is
significantly less than the radiance of the intense pulsed light.
As referred to herein, "intense pulsed light" is defined as polychromatic hght
delivered by at least one pulse, which may be supplemented by energy at radio
frequencies being directed at the target simultaneously with said light. Likewise
an "intense pulsed light source" is defined as an instrument that generates said
intense pulsed light or fluorescent pulsed light (FPL), wherein said instrument
may comprise an optical frequency shifter for shifting the wavelength of the
pulsed light being directed to the target.
Preferably, said pulsed light source is provided with an assembly connected to the
light source, for directing said light to said target, which assembly will be called
the light propagation assembly and the diverging location is the distal end of said
propagation assembly. Also preferably, a scattering unit is provided at said
diverging location, said unit comprising at least one scattering element, also called
hereinafter "diffuser," wherein each of said scattering elements or diffusers is
transparent to said intense pulsed light. As this term is used herein, "scattering"
means randomly changing the direction of adjacent light beams so that they
randomly diverge from one another, without any substantial change in the
wavelength of the incident light. Scattering is typically caused, and is caused in
the present invention, by the structure of a medium through which the light
propagates.
As referred to herein, "distal" means a location closer to a target, and therefore
more distant from the light source; "proximate" means a location more distant
from a target, and therefore closer to the light source; "axial" means a direction
from the center of the light source to the center of the target; and "transversal
means a direction perpendicular to the axial direction. Therefore, if the propagation assembly is so placed that the diverging location is close to a first
target, light having substantially the energy density of the generated pulsed light
will impinge on said first target, but light having a significantly reduced radiance
will impinge on a second target that is farther away from said diverging location.
If the first target is the intended target of an optical treatment and the second
target is an object that might be hurt by the intense pulsed light, the method of
the invention will combine the effectiveness of the optical treatment while
protecting objects that are not the intended targets of the treatment. Hereinafter,
it will be said that the distal end of the propagation assembly is "in the first
position" with respect to a target close to said assembly, tjφically the intended
target of an optical treatment, and "in the second position" with respect to an
object distanced from said assembly, typically an object that might be hurt by the intense pulsed light.
In another aspect, the method further comprises:
a) providing a diffusing unit transparent to the intense pulsed light
comprising at least one angular beam expander and at least one diffuser; b) attaching said diffusing unit to the distal end of the propagation
assembly of the intense pulsed light source (hereinafter, briefly, the propagation assembly); and
c) allowing the intense pulsed light to propagate through said at least
one angular beam expander and said at least one diffuser, whereby to scatter said intense pulsed light.
The energy density of the intense pulsed light at the first position (as hereinbefore
defined) of the distal end of the propagation assembly ranges from 1 to 100 J/cm2.
In one aspect, said first position is in contact with a target to which the intense
pulsed light is directed.
The radiance of the divergent intense pulsed light at the second position of the
distal end of the propagation assembly (as hereinbefore defined) is less than
10*kl*k2*(tΛl/3) J/cm2/sr, where k2=l and t is pulse duration of the intense
pulsed light in seconds, kl=l for a wavelength ranging from 400 to 700 nm,
kl=1.3 for a wavelength of approximately 570 nm, kl=1.6 for a wavelength of
approximately 830 nm, kl=3 for a wavelength of approximately 940 nm, and kl=5
for a wavelength greater than 1050 nm.
The wavelength of the intense pulsed light ranges from 400 to 1300 nm.
The duration of a pulse of the intense pulsed light ranges from 100 microseconds
to 1000 msec.
The intense pulsed light source is placed with its propagation assembly at the first
position for applications selected from the group of hair removal, skin
rejuvenation, wrinkle removal, treatment of vascular lesions, treatment of
pigmented skin, treatment of acne, treatment of herpes, treatment of psoriasis
and tattoo removal.
In another preferred embodiment, the method of improving bodily safety of
bystanders, according to the invention, further comprises the steps of: providing at
least one element of adjustable opacity attached to a handpiece of the intense
pulsed light source, placing said handpiece at a position in close proximity with
said target, increasing the opacity of said at least one element, generating light
from said source, allowing light rays to propagate through the skin and to be
backscattered, and allowing said backscattered light to be absorbed by said at
least one element.
As referred to herein, "handpiece" means a hand-held element having an
elongated, or any other suitable, shape, from which intense pulsed light exits and
which facilitates directing the intense pulsed light to a desired target. Said
handpiece is adapted to house the intense pulsed light source, propagation
assembly, and any control system needed for optimal operation of the invention.
Preferably, the opacity of the at least one element is increased synchronously with, or shortly before, the generation of the light and is decreased following the
generation of the light, whereby the skin is visible during those periods when light
is not emitted by the source. The activation time of the at least one element is up
to 1000 milliseconds and the deactivation time is less than 100 milliseconds.
In one aspect, the at least one element is attached externally to the handpiece.
The inclination of the at least one element relative to the handpiece is preferably
adjusted, in response to an instantaneous position of a bystander.
In another aspect, the visibility of the skin is increased by activating a
supplementary light source.
The present invention also comprises an apparatus comprising an intense pulsed
light source, for improving bodily safety of bystanders exposed to the light
generated by said source, comprising a handpiece, *a propagation assembly for
directing the hght of said source, contained within said handpiece, means
attached to said guide assembly, said means adapted to increase divergence of the
intense pulsed light at a given distance between the source and a target, whereby
at a first position of the distal end of said propagation assembly in close proximity
with said target the energy density of an exit beam from said distal end is
substantially equal to the energy density of the intense pulsed light and at a
second position more distant than said first position from said target the radiance
of the light emitted from said distal end is significantly less than the radiance of
the intense pulsed light.
In one preferred embodiment, the diverging means is also a scattering means.
In one aspect, the scattering means comprises a diffusing unit attachable to the
distal end of the guide assembly of the intense pulsed light source, said diffusing
unit including at least one diffuser that is transparent to the intense pulsed light.
In one aspect, the scattering means comprises a diffusing unit attachable to the
distal end of the propagation assembly of the intense pulsed light source, said
diffusing unit being selected from the group of at least one angular beam
expander, at least one micro-prism and at least one diffuser, or a combination
thereof.
The diffusing unit is preferably disposed between the intense pulsed light source
and the distal end of the propagation assembly.
In one aspect, the first position is substantially in contact with a target to which
the intense pulsed light is directed.
In one aspect, a coupler is disposed between the distal end of the propagation
assembly and the target.
In one aspect, the apparatus further comprises a mirror disposed between the
distal end of the propagation assembly and the target, said mirror preventing
direct view of the source.
The energy density at the first position of the distal end of the propagation
assembly ranges from 1 to 100 J/cm2, the pulse duration ranges from 100 microseconds to 1000 milliseconds, and the wavelength of the intense pulsed light
ranges from 400 nm to 1300 nm.
In one aspect, the apparatus further comprises a means for skin cooling, said skin
cooling means being adapted to cool the diffusing unit at the first position of the
distal end of the propagation assembly.
In one preferred embodiment, the apparatus further comprises a dual optical
generation system said dual system being operative to controllably generate either
monochromatic light or broad band intense pulsed light, comprising an apparatus
for improving bodily safety of bystanders exposed to a monochromatic light source,
comprising a means attached to the distal end of the propagation assembly 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 radiance of the light emitted from said
distal end is significantly less than the energy radiance of the monochromatic
light, said dual system being operative to controllably generate monochromatic
light and/or intense pulsed light.
The diverging means of the monochromatic light or of the intense pulsed light is
preferably a scattering means which comprises a diffusing unit attachable to the
distal end of the propagation assembly, said diffusing unit including at least one
diffuser that is transparent to the hght.
The diffuser is preferably produced such that any area thereof with a diameter of
0.75 mm scatters impinging light rays to such a degree that said area functions as
an extended diffused light source when viewed from a distance of 200 mm. The
diffuser is made from a material selected from the group of sapphire, glass and
polycarbonate.
Preferably, the diffuser has a first diffusive face and a second smooth face in
opposed relation to said first face, the diffuser being attached to the distal end of
the propagation assembly in such a way that said second face is distal with
respect to said first face.
In another preferred embodiment, the apparatus for improving bodily safety of
bystanders, according to the invention, comprises at least one element of
adjustable opacity externally attached to a handpiece of the intense pulsed light
source and so positioned so as to absorb substantially most of the subcutaneously
backscattered light resulting from the generation of said intense pulsed light
directed to a skin target.
In one aspect, the opacity of said at least one element is adjustable upon
generation of said light.
The element is selected from the group of a liquid crystal window, a spectral
density filter, an attenuation filter, a mechanical shutter, or a combination
thereof.
The opacity of a density filter is preferably a predetermined constant value in
accordance with the spectrum of intense pulsed light.
In one aspect, the apparatus further comprises control circuitry for synchronizing
the opacity adjustment of the at least one element, in response to the generation of
the light. The control circuitry is operative to cause the at least one element to be
substantially transparent during those periods when light is not emitted by the
source.
In another aspect, the apparatus further comprises a supplementary light source
externally attached to a handpiece of the intense pulsed light for increasing skin
visibility.
In one aspect, the attenuation filter is an optical band pass filter. The wavelength
of the light that passes through the filter preferably is based on the chromophore
of a lesion to be treated by the light.
In another aspect, the attenuation filter is a spectral filter which blocks the
backscattered light and transmits the supplementary light.
The present invention is also directed to a method of aesthetic improvement,
comprising:
a) providing a source for generating intense pulsed light and a light
propagation assembly by which said hght is directed to a target;
b) positioning the distal end of said propagation assembly at a first
position in close proximity with said target;
c) causing said source to generate at least one pulse of polychromatic
light;
d) diverging said pulsed light at a location between said source and said
target, whereby at said first position the energy density of light exiting from said
diverging location is substantially equal to the energy density of the intense
pulsed light; and
e) effecting an aesthetic improvement, wherein the radiance of the light emitted from said diverging location, at a second
position distant from said target, is less than 10*kl*k2*(tAl/3) J/cm2/sr, where
k2=l and t is pulse duration of the intense pulsed light in seconds, kl=l for a
wavelength ranging from 400 to 700 nm, kl=1.3 for a wavelength of
approximately 570 nm, kl=1.6 for a wavelength of approximately 830 nm, kl=3 for a wavelength of approximately 940 nm, and kl=5 for a wavelength greater
than 1050 nm.
In one aspect, the energy density is at least 1 J/cm2 at the first position.
In one aspect, the aesthetic improvement is selected from the group of hair
removal, skin rejuvenation, wrinkle removal, treatment of vascular lesions,
treatment of pigmented skin, treatment of acne, treatment of herpes, treatment of
psoriasis and tattoo removal.
In another aspect, the aesthetic improvement is self-effected without use of
protective eyeglasses. During a self-effected aesthetic improvement, a patient
positions the diverging location in close proximity to his skin, holds a handpiece of
the light source, and generates the light while viewing and selecting areas of the
aesthetic improvement.
Brief Description of the Drawings
In the drawings:
Fig. 1 is a schematic drawing of a prior art intense pulsed light source;
Fig. 2 is a schematic drawing which demonstrates the potential damage to
an eye associated with the firing of a prior art intense pulsed light source;
Fig. 3 is a schematic drawing of an intense pulsed light source in
accordance with the present invention, showing an optical effect that results as
intense pulsed light is scattered;
Figs. 4a-e illustrate different configurations of diffusing units attachable to
an intense pulsed light source;
Figs.5a-c schematically illustrate different configurations of devices adapted
to conduct heat from a heated diffuser, following the generation of an intense
pulsed light source, in accordance with the present invention;
Figs. 6a-h schematically illustrate different configurations of a
backscattering protection unit;
Fig. 7 is a schematic drawing of a dual laser and IPL generator, in
accordance with the present invention;
Fig. 8 is a picture of an arm of the patient, illustrating the efficacy of
diffused intense pulsed light, in accordance with the present invention; and
Figs. 9a-b are pictures of the distal end of an intense pulsed light source
without and with a diffuser, respectively, showing the lowered radiance that may
be reahzed with the use of the present invention.
Detailed Description of Preferred Embodiments
The present invention is a device for improving bodily safety during exposure to
an intense pulsed light (IPL) source, which device is adapted to diffuse the intense
pulsed light, the diffused light providing the required energy density of light for
desired applications at a very short distance but being inherently safe to the eyes
of bystanders.
In a first embodiment, the IPL source is provided with a diffusing unit which
causes the light exiting from said unit to be scattered. The exit light is scattered to
such a degree that the radiance of said exit light is less than the accessible
emission limit (AEL), and therefore is not injurious to the eyes of bystanders that
are in a direct line of view thereto.
Fig. 1 illustrates a prior art intense pulsed light source designated generally as 1,
as disclosed in US Patent No. 5,683,380, which is suitable for aesthetic treatments
at a target skin location 14. IPL source comprises high intensity pulsed flash lamp
4, which generates polychromatic light, and light guide 8. Generated light rays
such as 5 and 6 are either reflected from reflector 7 into light guide 8 or propagate
directly through light guide 8 without any intermediate reflection. The light
energy is transmitted through the light guide and may be reflected by wall 9 of the
light guide towards the skin. The light exits light guide 8 through distal end 11
thereof, which is planar and transparent to the non-coherent light. Distal end 11
is generally placed in contact with target skin location 14, or is extremely close
thereto. The light impinges the skin with a minimal loss in energy density and
due to the extremely small spacing between the distal end 11 and skin 14. The
light energy which propagates through the skin is scattered to a large degree
within the skin and just a small fraction thereof reaches hair follicles 2, blood vessels 3 or collagen bundles 12. Concerning hair follicles, for example, the
scattered light impinges and destroys a hair strand contained within a given
follicle. Intense pulsed light sources are broad band sources, resulting in the
absorption of a percentage of the energy, for example, in one part of the spectrum by melanin in hair filaments and a percentage of the energy in another part of the
spectrum by blood vessels.
The selected spectral band and pulse duration of the IPL source depend on the
specific application. The energy density of the IPL source at distal end 11 of the
light guide, or upon impinging skin 14, has to be above a predetermined threshold
level in order to be efficacious. For example, IPL sources are operated at a
relatively high energy density of 7 -55 J/cm2 for hair removal. Some systems
utilize trains of 2-3 pulses, with each pulse having a duration of approximately 2.5
msec at a wavelength substantially above 700 nm (Gold MH, Dermatol. Surg. 1997, 23(10), 909-1). Photorejuvenation is performed at an energy density of 36
J/cm2 with three pulses, while each pulse has a duration of 2.5 msec (M.B.Taylor,
ASLMS Abstracts, April 2001, Abstract 130). In other systems, an energy density
level of 10 J/cm2 is used. The angular divergence of intense pulsed light may often
be a half angle of 50 degrees, or a solid angle of approximately 2 steradians,
depending on the dimensions of the light guide.
Referring now to Fig. 2, potential eye injury when directly staring at prior art IPL
source 1 may be demonstrated. Light rays 5 or 6 are reflected by wall 9 of light
guide 8, and since they do not necessarily impinge eye 20 they are not definitively
injurious to the eye. However, a direct line of sight 22 may nevertheless be
established between flash lamp 4 and eye 20, causing eye 20 to be exposed to the maximum radiance of the flash lamp. The radiance of the light propagating
directly from the light guide, as represented by direct line of sight 22, is much
greater and more injurious than that which exits distal end 11, since the solid
angle spanned by flash lamp 4 is considerably less than that spanned by distal
end 11, following the reflection of light rays 5 and 6 by wall 9.
Fig. 3 illustrates IPL source 25, in accordance with an embodiment of the present
invention. The distal end of light guide 8 is provided with diffusing unit 15
attached thereto by any means well known to those skilled in the art. The light
guide may be divergent in order to increase the angular divergence of the
propagating light. Diffusing unit 15 comprises diffuser 19, e.g. made of sapphire.
By adding such a diffuser with a diffusing angle of A to the light guide, the image
of the flash lamp is blurred on the retina and the flash lamp seems to be an
enlarged extended diffusing source 31, with a width larger than flash lamp 4.
As referred to herein, "diffusing angle" is defined as the angular distribution of
energy that results following the interaction of light with a diffuser, at which
angle the energy density is one-tenth that of the maximum energy density of the
light. A diffuser having a full angle ranging from 4 to 120 angles is suitable for the
present invention.
Scattering is achieved by means of minute irregularities of a non-uniform
diameter formed on the substrate of diffuser 19. Diffuser 19 is preferably produced
from thin sand blasted or chemically etched glass or sapphire, e.g. having a
thickness from 0.1 to 1.0 mm, or a thin sheet of non-absorbing light diffusing
polymer, e.g. having a thickness of less than 500 microns, such as light diffusing polycarbonate.
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 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. 4a.
Diffuser 19 may be produced in several ways:
• Sandblasting the surface of a plate of glass, sapphire, acrylic or
polycarbonate with fine particles having a size ranging from 1 to 200 microns;
• Sandblasting the surface of a mold plate with fine particles having a size
ranging from 1 to 200 microns, 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;
• Etching the surface of a glass or sapphire plate by chemical means, such
as with hydrogen fluoride;
• Etching the surface of a glass plate with a scanned focused CO2 laser
beam; and
• Applying a thin sheet of light-diffusing polymer, such as a polycarbonate
sheet, to a glass plate.
Diffuser 19 is positioned such that its diffusive side faces the flash lamp, whereas
its smooth side faces the skin so that any liquid such as sebum which may adhere
to the diffuser will adhere to the distal smooth end thereof and will therefore not
modify its diffusive properties. The diffuser may be similarly produced in other
ways, such as by sandblasting, such that it conforms with FDA eye safety
standard 1040.10 21 CFR Ch.l. Diffuser 19 is preferably produced from sapphire
which has a high thermal conductivity, and may also be produced from other
materials as well such as glass or highly durable polymers.
The AEL for visible and near-infrared radiation exiting a diffusing unit, for which
protective eyeglasses are unnecessary, is based on an extended diffuser source
defined by ANSI Z 136.1 as 10*kl*k2*(tAl/3) J/cm2/sr, where t is in seconds and
kl=k2=l for a wavelength of 400-700 nm, kl=1.25 and k2=l at 750 nm , kl=1.6
and k2=l at 810 nm , kl=3 and k2=l at 940 nm and kl=5 and k2=l at a
wavelength of 1060 to 1400 nm.
The improved eye safety of the present invention relative to the prior art may be
realized by determining the AEL associated with an exemplary IPL source- a
Xenon flash lamp having a diameter of 2 mm, a length of 40 mm, an energy
density of 30 J/cm2, and a spectral band of 645 - 1100 nm, generating a pulse
duration of 30 milhseconds- propagating through a light guide having a length of
120 mm and a distal end having a size of 10x40 mm.
The radiance R of the flash lamp without a diffuser, as in the prior art, is equal to
the energy density of the light (30 J/cm2) divided by the solid angle spanned by the flash lamp light (π, as for any black body light source), further divided by 2,
due to 50% backward light propagation and multiplied by the ratio of the width of
the light guide distal end to that of the flash lamp (10:2) . As a result, R= 75/3.14,
and is approximately equal to 24 J/cm2/sr, approximately 5 times greater than an
AEL of 5 J/cm2/sr, as specified by the ANSI Z 136 .1 standard for a pulse duration
of 30 milliseconds.
In contrast, with the addition of a diffuser, the flash lamp diameter is blurred to a
size of A x L, where A is the diffusing half angle in radians and L is the light guide
length. Therefore, for a diffusing angle of 10 degrees (equal to 1/6 radians), which
is typical for a chemically etched diffuser, and a light guide length of 120 mm, a
blurred flash lamp diameter of 20 mm results, corresponding to a reduction in
radiance by a factor of 10. As a result, the radiance of a diffused IPL source is
approximately one-half of the eye-safe limit and therefore the IPL source may be
operated without need of protective eyeglasses.
During treatment, the distal end of the light guide is placed on the skin target, or
in close proximity thereto. Accordingly, it will be appreciated that the addition of a
diffuser to the distal end of the light guide does not affect the treatment efficacy of
the IPL source. The energy density of the light which impinges tissue, after being
scattered by the diffuser, is substantially equal to that of the light emitted by the
flash lamp, due to the proximity of the distal end of the light guide to the skin target.
Other configurations for improving eye safety during exposure to intense pulsed
light are shown in Figs. 4a-e, in accordance with the present invention. In Fig. 4a
an array of micro-lenslets 51 is employed, such as an array available from Fresnel Optics Corp. (USA), wherein each lenslet has a diameter of 0.7 mm. A micro-
lenslet, as referred to herein, has a semicircular cross section, with a diameter
ranging from 0.1-2.0 mm. In Fig. 4b two diffusers 52 and 53 are used. In Fig. 4c
the IPL source is provided with a metallic back reflector 60, without a light guide.
Back reflector 60 is etched as well as transparent distal end 54, to allow for
increased scattering. In Fig. 4d a reflecting mirror 55 is installed, which conceals
flash lamp 34 and prevents direct view of a high radiance zone. In Fig. 4e a pair of
concave and convex reflectors 64 and 65, respectively, are used to thereby conceal
flash lamp 34 and prevent staring directly at the flash lamp. Light guide 70 may
be used in conjunction with the configuration of Fig. 4e to further reduce the
emitted radiance. The light which exits from diffuser 53 is received by hght guide
70 and is reflected within its inner wall, resulting in wide angle diffusing from the
entire exit surface of the light guide. A diffusing unit may also be provided with an
array of micro-lenslets, micro-prisms or a combination thereof.
Transparent skin cooling devices are often used in conjunction with skin
treatments. Some skin cooling devices utilize a low temperature transparent
liquid flowing across the distal end of a handpiece in contact with the skin in order
to dissipate the heat generated by the IPL. Other skin chillers utilize a
thermoelectric unit to chill the distal end of a handpiece and to thereby transfer
heat from the skin. However the prior art devices do not scatter IPL and
consequently do not reduce the risks associated with eye exposure to the IPL.
In one embodiment of the present invention, a device for scattering IPL is also
provided with a coohng device. As shown in Fig. 5a, transparent cooling fluid ιsι,
e.g. a low temperature gas or liquid of approximately 4°C, flows across diffuser
180 having a high thermal conductivity, e.g. a sapphire diffuser. Cooling fluid 151
flows through conduit 171, such that it is admitted to the cooling device at port
173 and exits therefrom at port 174. The distal end of the cooling device is in
contact with skin target 185, and conducts heat from the heated skin. In Fig. 5b,
cooling fluid 151 passes through vessel 190, thereby increasing its dwelling time
in the vicinity of diffuser 195. In Fig. 5c thermoelectric chiller 140 chills diffuser
147, the distal end of which is in contact with skin target 185, and may also chill
light guide 145.
Figs. 6a-h illustrate another embodiment of the present invention in which a
handpiece, through which light propagates from an IPL source, is provided with a
liquid crystal backscattering protection unit for attenuating light backscattered
from the skin, which would normally cause an operator to suffer from eye fatigue.
Operators of IPL sources are subject to long term exposure of trains of flash light
pulses reflected from the skin of a patient. Although each optical pulse reflected
from the skin is diffused and is not capable of burning a portion of the retina, the
cumulative effect of a train of pulses results in the tiring of an eye of an operator
since the pupil repetitively expands and contracts in response to the change in
radiance of the light which is incident on the eyeball.
The effect of eye tiring as a result of backscattered radiation is illustrated in Fig.
6a, wherein light guide 202 is positioned to be substantially in contact with skin
201. Light ray 200 which is reflected by the wall(s) of light guide 202 propagates
through skin 201 and emerges from the skin as reflected rays 203 due to internal
backscattering within the skin. Rays 203 impinge eye 1204, resulting in eye tiring
after extended exposure.
As shown in Fig. 6b, eye tiring is prevented by adding a shield around, and
perpendicular to, the distal end of a handpiece of the IPL source. In the illustrated
example, normally transparent liquid crystal window 205, e.g. of 2 mm thickness,
is affixed to the distal end of light guide 202. When not activated, window 205 is
transparent and skin 201 is visible to eye 204 by line of sight 210. Window 205 is
provided with transparent electrodes 206 and 207 connected to a power supply
(not shown) by wires 208 and 209, respectively.
When liquid crystal window 205 becomes activated, e.g. by a low voltage of 6V, as
shown in Fig. 6c, its optical properties change and the window becomes opaque to
reflected ray 203. Eye 204 is no longer exposed to reflected ray 203 and eye tiring
is therefore prevented. Window 205 is activated synchronously with, or shortly
before, e.g. 10 msec before, the activation of a flash lamp, so that it will be opaque
during the short duration of flashlight emission from the IPL source. Window 205
may be advantageously activated in accordance with a predetermined timing
sequence by means of control circuitry (not shown). Since the duration of a
treatment pulse is usually not longer than 300 msec and the delay between
successive pulses is approximately 1-3 seconds, the short-duration opacity of the
liquid crystal allows the skin to be visible during those periods when pulses are
not emitted. It will be appreciated that as the transversal dimension of window
205 increases, i.e. perpendicular to the distal direction, more reflected rays will be
absorbed by the liquid crystal. The transversal protrusion of one side of window
205 from light guide 202 ranges from 5-100 mm, and is preferably less than 40
mm.
Fig. 6d schematically illustrates a device, generally indicated by numeral 510,
which comprises IPL source 530 that generates hght reflected by reflector 535 and
propagated through light guide 520, handpiece 542, which encircles the light guide
and is held in close proximity to skin target 555, and backscattering protection
unit 540, which is attached externally to handpiece 542. Backscattering protection
540 may comprise a plurality of assemblies 537 that are pivotally displaceable
with respect to the handpiece 542 and that house a corresponding liquid crystal
window 541. Electrical wires 543 and 544 in contact with translucent conducting
surfaces 545 and 546, respectively, of an assembly 537 are adapted to change the
opacity of the corresponding liquid crystal window 541.
Light 547 which exits the distal end of light guide 520 and propagates through
skin 555 is partially scattered, as indicated by numeral 548, by the skin and may
repeatedly impinge eye 523 of an operator. By generating a potential between
surfaces 545 and 546, the opacity of window 541 is increased and backscattered
light 548 which propagates through the instantaneously darkened window 541 is
considerably dimmed. By deactivating the potential, the transparency of window
541 is reset. Since a liquid crystal window is effectively a light polarization device,
an activated window 541 dims to some extent the visibility of the treatment site
which is normally illuminated by non-polarized room light 549. Room light 549
passes twice through window 541- as it propagates towards skin target 555 and as it is reflected therefrom and impinges eye 523. As shown in Fig. 6e, backscattering
protection unit 540 may comprise a high intensity, miniature light source 550 for
the illumination of skin 555, which is externally attached to handpiece 542 at an
attachment point between assembly 537 and skin 535. Lamp 550 may emit white
light, thereby compensating for the attenuation of room light 549 at skin target
555.
An exemplary liquid crystal window 541 is a homogenous analog dye guest host
liquid crystal shutter produced by CRL Opto, UK, which has a response time of 20
milliseconds from an activated to deactivated state and a decay time of 70
milliseconds, and is therefore suitable for applications for which visibility cannot
be impaired more than 300 milliseconds. The transition from an activated state to
a deactivated state is at 3.3 V, and since the window has a sufficiently low power
requirement, small Lithium batteries may in use for tens of hours of operation
without replacement.
Another exemplary liquid crystal window is a matrix of liquid crystal pixels,
wherein a thin-film transistor is located at each pixel intersection, requiring a
relatively low amount of current to control the luminance of a pixel. The average
optical transmission of the liquid crystal may therefore be varied with a wide
dynamic range by switching the current through some of the transistors.
An exemplary light source 550 is a white LED, such as the "Photon Microlight II"
produced by L.R.I, OR, USA, having a width of approximately 3 mm. The
illumination of such a light source is maximum at a distance of a few centimeters,
generating a temperature of 6500 deg Kelvin color with a sufficiently low power
consumption such that two 3-Volt Lithium batteries are sufficient for over 100
hours of operation.
As shown in Fig. 6f, each backscattering protection unit 540 may comprise a
density filter 551 in addition to liquid crystal window 541. Density filter 551,
which has a predetermined constant opacity in accordance with the spectrum of
the IPL, absorbs some radiation of the backscattered light, permitting only a
fraction thereof to be transmitted. Density filter 551 may be advantageously
employed during the generation of a very bright backscattered pulse, for which a
liquid crystal window could not provide adequate attenuation, e.g. following
inadvertent separation of the distal end of the handpiece from a skin target. The
lack of visibility at the target skin target due to the high attenuation effected by a
density filter may be compensated by increasing the illumination of the low power-
consumption light source 550 upon conclusion of the firing of the IPL, e.g. after a
train of pulses.
As shown in Fig. 6g, each assembly 537 provided with a liquid crystal window may
be pivotally displaceable with respect to handpiece 542. The angular disposition of
assembly 537 is adjustable, so as to provide optimal protection to eye 523, as the
operator changes position, for example, from a sitting to a standing position, or moves side to side.
As shown in Fig. 6h, backscattering protection unit 540 may comprise eye
protection shield 581, e.g. having a conical shape, which may be used for several
applications such as for hair removal. Shield 581 may be a low cut-off filter at the
invisible 810 nm wavelength, i.e. is adapted for filtering backscattered IPL at a
wavelength longer than 810 nm. Light at a wavelength longer than 810 nm is
suitable for treating hair without damaging the epidermis. If the optical
transmission of shield 581 at a wavelength below 810 nm is high, the illumination
of room light 549 may be sufficiently high so as to provide adequate visibility at
the skin target. However, if the room illumination is not sufficiently high, light
source 550 may supplement the illumination.
Fig. 7 illustrates a dual system for aesthetic treatments. Dual system 380
incorporates a power supply which can energize both an IPL source 383, which is
insertable through port 381, and laser source 384, which is insertable through
port 382. Each of the IPL source 383 and laser source 384 is provided with a
diffusing unit at the corresponding distal end so that the light which exits
therefrom is eyesafe to a bystander. Co-pending International Patent application
PCT/IL02/00635 by the same applicant, describes an eye-safe laser unit suitable
for aesthetic treatments, wherein a diffusing unit is attached to the distal end of
the laser source. Similarly other configurations for converting highly risky
monochromatic laser units, which are suitable for aesthetic treatments, into non¬
coherent, eye-safe units are described therein.
Example 1
Fig. 8 illustrates the efficacy of diffused intense pulsed light, according to the present invention.
A single IPL pulse having an energy density of 20 J/cm2 and a pulse duration of 20
milliseconds was directed at an arm 113 of a patient having a hair density of
approximately 40 hairs/cm2. A sapphire diffuser, which was thermoelectrically
chilled to a temperature of approximately 4°C, with a diffusing angle of 10 degrees
was attached to the distal end of the light guide of the IPL source. A cut-off
spectral filter with a surface area of 8 x 40 mm, which transmits light at a
wavelength longer than 750 nm, was attached externally to the handpiece of the
IPL source.
The arm of the patient was marked with a plurality of dots 117 to indicate the
skin target at which the IPL was to be directed, an area of 8 x 40 mm. The pulse of
IPL light was fired on October 27, 2002 and the shown picture was taken on
December 15, 2002, at which time the hair density within the treatment zone was
less than 4 hairs/cm2. The hair density in the untreated zone was equal to the
hair density within the treated zone before the treatment. It can be seen that an
IPL source provided with a diffusing unit at the distal end thereof is efficacious for
hair removal.
The addition of a diffusing unit can be equally effective for other applications. A
spectral band greater than 550 nm can be utilized for the treatment of vascular
lesions, greater than 400 nm for the treatment of acne, greater than 750 for hair
removal of subjects with dark skin, and greater than 550 nm for
p hotore j uvenation.
Figs. 9a and 9b are pictures of the distal end of the IPL source used for the
aforementioned treatment without and with a 10 degrees sapphire diffuser,
respectively. A blinding flash lamp 30 is seen in Fig.9a, whereas the addition of
diffuser 32 resulted in a safe low-radiance, extended diffusing surface, as shown in
Fig. 9b. A filter was added to the camera before the picture of Fig. 9a was taken,
so as to ensure camera integrity, and it will be appreciated that the radiance
emitted by flash lamp 30 was much greater than the light that exited diffuser 32.
Example 2
A small-sized IPL source, which generated a relatively low energy density of 5
J/cm2, can be used as a shaver for home use, necessitating shaving only once in
two weeks.
The operator may place a handpiece having a width of 3 cm and a length of 5 cm
on his own face. After the operator depresses the activation switch located on the
handpiece with his thumb, he may shave his face with IPL while viewing his
reflection in a mirror, without need of protective eyeglasses.
A Xenon flash lamp, which has a diameter of 1 mm and a length of 20 mm, with a
spectral emission of 550 nm, thereby being greatly absorbed by melanin, may be
employed. One fired pulse may remove facial hair from an area of 4 x 20 mm. The
pulse duration may be 3 milliseconds, to ensure efficacy at the low energy density
5 J/cm2, and the pulse repetition rate may be once in 3 seconds. The face of the
operator may be completely shaved within 3 minutes.
A sapphire diffuser having a half-angle of 10 degrees may be attached to the distal
end of the handpiece, at a distance of 12 mm from the flash lamp. With the
aforementioned parameters, the flash lamp diameter will appear to be 2 mm and
the radiance will be equal to AEL, a value of approximately 2 J/cm2/sr for a pulse
duration of 3 milhseconds. Therefore shaving could be safely conducted without
needing protective eyeglasses. The IPL will not be injurious to the eyes of the
operator, even when the handpiece is separated from his face during the firing of
the light.
As can be seen from the above description, a diffusing/diverging unit of the
present invention, which is mounted to the exit aperture of an intense pulsed light
source induces the exiting light to be divergent and/or scattered at a wide angle.
As a result, the exiting light has a small enough radiance not to be injurious to the
eyes of observers which may accidentally stare directly at the hand piece.
Nevertheless, the exiting light generally retains a similar level of energy density
as the light generated from the exit aperture when the diffusing/diverging unit is
very close or essentially in contact with the target, and is therefore capable of performing various types of treatment. Protective eyeglasses are generally not
needed, particularly since a backscattering protection unit is added to the
handpiece, and therefore an IPL source may be operated in an aesthetic clinic or
even in one's home by personnel without any medical training, in a less
cumbersome and safer way than which was known heretofore.
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.