WO2001041267A9

WO2001041267A9 - Multipulse dye laser

Info

Publication number: WO2001041267A9
Application number: PCT/US2000/032839
Authority: WO
Inventors: James C Hsia; Anthony D Quaglia
Original assignee: Candela Corp
Priority date: 1999-12-06
Filing date: 2000-12-04
Publication date: 2002-05-23
Also published as: ATE399378T1; JP2003530686A; US6364872B1; US6512782B1; DE60028077D1; ATE326784T1; WO2001041267A1; EP1238450A1; EP1238450B1; DE60028077T2; DE60039308D1

Abstract

A method for generating a long effective pulse duration output beam of laser radiation using a flashlamp-excited dye laser is described. A spaced series of excitation pulses is electronically generated using a pulse forming module. The series of excitation pulses are provided to a flashlamp-excited dye laser, which generates an output beam of laser radiation. The output beam is comprised of a series of spaced micropulses of laser radiation which, in combination, provide a long effective pulse duration.

Description

MULTIPULSE DYE LASER

Field of the Invention The present invention relates generally to the field of lasers. More specifically, this invention relates to a method and laser apparatus for producing a pulsed output beam of laser

radiation having a long effective pulse duration.

Background of the Invention

Facial telangiectasia (i.e., abnormal, dilated blood vessels) is a somewhat common occurrence in individuals with fair skin. Individuals having facial telangiectasia often seek cosmetic treatment for these vessels. The flashlamp-excited pulsed dye laser is an established device for the treatment of various cutaneous vascular lesions including facial telangiectasia. When treated with such a dye laser, most vessels can be cleared with a single treatment, and

nearly all vessels can be cleared within three treatments.

Flashlamp-excited pulsed dye lasers used for treatment of facial telangiectasia (and

various cutaneous vascular lesions) typically operate at a wavelength between 585 and 600

nanometers (nm) and a pulse duration of 450 microseconds (μsec) to 1.5 milliseconds (msec).

One of the treatment side effects particularly bothersome to patients is acute post-treatment purpura (i.e., superficial hemorrhage characterized by blue/black discoloration). Purpura is always bothersome, particularly when it appears on the face. Purpura can take one to three weeks to fully resolve and is often quite disruptive in a person's work and social schedules. The acceptance of dye laser treatment would be considerably enhanced if purpura could be minimized

or eliminated. The cause for purpura in pulsed dye laser treatment of vascular lesions is generally

thought to be caused by the extravasation of blood components from the rupture of the skin's

microvasculature, due to the rapid vessel heating produced by the relatively short pulse duration of the laser. Researchers have conjectured that if the pulse duration of the dye laser could be lengthened to a duration that is short compared to the thermal relaxation time of the abnormal

vessels but long compared with the thermal relaxation time for the normal microvasculature, then

the rupture of these vessels could be minimized or avoided. (Anderson, R.R. "Laser-Tissue

Interactions," Goldman, M.P., Fitzpatrick, R.E., Cutaneous Laser Surgery (St. Louis, Mosby,

1994), pp. 9-11.)

Various lasers currently used to treat facial telangiectasia generate a continuous pulse having a long pulse duration (i.e., greater than 10 msec). For example, the Aura™ laser

(manufactured by Laserscope, Inc. of San Jose, CA) and the Versapulse™ laser (manufactured by Coherent, Inc., Medical Group, of Santa Clara, CA) are both solid-state lasers capable of generating output beams having a 10-20 msec pulse duration. Little or no purpura has been

observed using these lasers. However, the depth of penetration of the output beam from these solid-state lasers is less than that of a pulsed dye laser beam due to the shorter wavelength (i.e.,

532 nm). There is also stronger melanin absorption in the skin at this shorter wavelength.

Consequently, the efficacy in treating deeper and larger telangiectasias is reduced when using one of these solid-state lasers.

The difficulty in forming a continuous output pulse having a long pulse duration with

a flashlamp-excited dye laser is that accumulation of dye molecules in metastable electronic states, thermal distortions in the liquid dye medium (i.e., the gain medium) and photodegradation

of the dye all can cause the laser action (i.e. lasing) to self-terminate. This self-termination

occurs when the lasing threshold (i.e., the energy level at which laser action occurs) rises due to these conditions. With a constant amplitude excitation pulse, when the lasing threshold rises

above the amplitude of the excitation pulse, lasing terminates.

U.S. Patent No. 5,287,380 discloses a method of generating an excitation pulse with a

ramped amplitude to extend the duration of the output beam of a flashlamp-excited pulsed dye

laser. U.S. Patent No. 5,598,426 discloses a ramping technique in which the amplitude of the

excitation pulse changes in coordination with the lasing threshold to achieve an output beam

pulse of extended duration. These patents describe methods that extend the pulse duration of the output beam to about 2 milliseconds. U.S. Patent No. 5,746,735 describes optically combining the output beams of multiple lasers to obtain an output beam having a pulse duration of at least

one millisecond. However, this technique requires 1 to 2 lasers for each millisecond of pulse

duration.

A principle object of the present invention is to provide a flashlamp-excited pulsed dye laser having a long effective pulse duration (e.g., on the order of 5 to 40 milliseconds) so as

to effectively treat facial telangiectasia (and various other cutaneous vascular lesions) with

reduced post-treatment purpura.

Summary of the Invention The invention relates to an apparatus and method for generating an output beam of

laser radiation having a long effective pulse duration (e.g., on the order of 5 to 40 milliseconds). For certain applications, a long effective laser pulse duration is desirable to allow thermal

diffusion to occur during the time of laser energy deposition. An example is treating facial

telangiectasia effectively while avoiding purpura. Another example is laser cutting and welding

of metals and non-metals. While preferred embodiments include a flashlamp-excited pulsed dye laser, the principles of the invention can be advantageously applied to any laser with a

dynamically increasing lasing threshold. Lasers with dynamically increasing lasing threshold include all lasers in which the lasing transition terminates in an energy level with appreciable thermal population. An example is the holmium laser operating near 2 micron wavelength. In

this case, the lasing threshold increases during a laser pulse due to the increase in lower laser

level population caused by the increase in temperature of the lasing medium. The principles of

the present invention can also be advantageously used when the desired laser pulse duration is

difficult to generate because the excitation energy required to maintain the laser above lasing

threshold for the entire pulse is too great.

A laser incorporating the principles of the invention generates an output beam

comprised of a series of micropulses of laser radiation. The series of micropulses constitute an output beam having a long "effective" pulse duration that has been shown to be effective in

therapeutic treatment of cutaneous vascular legions while minimizing the undesired side effects

of purpura or other hyper-, hypo-pigmentation abnormalities.

In one aspect, the invention features a method of generating a pulsed output beam of laser radiation having a long effective pulse duration in a flashlamp-excited dye laser. This

method includes the steps of generating electronically a spaced series of excitation pulses,

driving the flashlamp-excited dye laser with the series of excitation pulses, and producing an

output beam comprised of a series of spaced micropulses of laser radiation which, in

combination, have a long effective pulse duration.

In one embodiment, each pulse within the spaced series of excitation pulses has an

amplitude that increases in coordination with an increasing lasing threshold for the flashlamp- excited dye laser. In another embodiment, a tuning element is adjusted in coordination with each

pulse within the spaced series of excitation pulses to vary the wavelength of each micropulse. In

another embodiment, the effective pulse duration of the output beam is at least 5 milliseconds. In another embodiment, each micropulse has a pulse duration of at least 10 microseconds. In another embodiment, each micropulse delivered to the skin has a fiuence less than 5 j/cm². In

another embodiment, the series of micropulses delivered to the skin has a total fiuence greater

than 6 j/cm . In another embodiment, each micropulse has an energy level that is less than half of the total energy of the series of micropulses. In another embodiment, the series of micropulses

has a total energy greater than 1 Joule. In another embodiment, the output beam of laser radiation is directed at the skin of a patient to treat a cutaneous vascular lesion. In another

embodiment, the pulse parameters are selected to minimize the formation of purpura. In another

embodiment, the effective pulse duration of the output beam is between about 5 milliseconds and

about 40 milliseconds.

In another aspect, the invention features a flashlamp-excited dye laser for producing a

pulsed output beam having a long effective pulse duration. The laser includes a pulse forming module, a flashlamp and a lasing medium. The pulse forming module generates a series of spaced excitation pulses. The flashlamp is electrically connected to the pulse forming module

and receives the series of spaced excitation pulses. The flashlamp uses the excitation pulses to

produce a series of light pulses. The lasing medium can include a liquid dye mixture. The liquid

dye medium receives the series of light pulses from the flashlamp and produces an output beam

comprised of a series of spaced micropulses of laser radiation which, in combination, have a long

effective pulse duration.

In one embodiment of the laser, each pulse within the spaced series of excitation

pulses is generated with increasing amplitude in coordination with an increasing lasing threshold

for the flashlamp-excited dye laser. In another embodiment, a tuning element is adjusted in coordination with each pulse within the spaced series of excitation pulses to vary the wavelength of each micropulse. In another embodiment, the effective pulse duration of the output beam is at

least 5 milliseconds. In another embodiment, each micropulse has a pulse duration of at least 10 microseconds. In another embodiment, each micropulse has an energy level less than half of the

total energy of the series of micropulses. In another embodiment, the series of micropulses has a

total energy greater than 1 Joule. In another embodiment, the output beam of laser radiation is

used to treat a cutaneous vascular lesion on a patient's skin.

Brief Description of the Drawings

The foregoing and other objects, features and advantages of the present invention, as

well as the invention itself, will be more fully understood from the following description of

preferred embodiments, when read together with the accompanying drawings, in which:

FIG. 1 is a block diagram of an embodiment of a multipulse dye laser according to the

invention.

FIGS. 2 A and 2B are graphical illustrations of a series of excitation pulses and the

corresponding output beam in accordance with the invention.

FIG. 3 is a block diagram of an embodiment of a pulse forming module according to

the invention.

Detailed Description

FIG. 1 depicts a laser system 10 incorporating the principles of the invention. The

laser system 10 includes a lasing medium 14 comprising an elongated dye cell in which a dye

carried by a liquid is dissolved. The lasing medium 14 preferably is maintained at a uniform and

constant temperature. A pulse forming module 20 includes pulse forming networks 22 and

switching networks 26. The pulse forming networks 22 generate a spaced series of excitation

pulses (described in more detail below). The pulse forming module 20 applies each excitation pulse through the respective switching networks 26, to a flashlamp 30 to excite the lasing

medium 14. The power supply 18 provides the energy to the pulse forming networks 22. A

simmer supply 28 supplies a low level current 80 (FIG. 2 A) to the flashlamp 30 to develop a significant level of ionization in the flashlamp prior to discharge of the flashlamp.

Each pulse generated by the pulse forming module 20 causes the flashlamp 30 to

discharge, producing a pulse of light of high intensity. More specifically, the high intensity light

emanating from the flashlamp 30 is directed to the lasing medium in the dye cell 14. A specular

or diffuse reflector (not shown), or other optical element, can be used to direct the light to the dye cell. The lasing medium can include a liquid dye mixture. The light from the flashlamp 30 is absorbed by the lasing medium 14 causing dye molecules to move from the ground state to

excited singlet states. As the excited molecules return to the ground state, photons of a particular

wavelength are emitted. Some of the light emanates from apertures 34, 38 located at each end of

the dye cell 14. First and second mirror assemblies 42, 46, in combination, constitute an optical system for the laser. The first mirror assembly 42 is fully reflective and returns emanated light

back into the dye cell.

The first mirror assembly 42 can include a wavelength tuning element 48 to tune the

output beam within the gain curve of the dye solution. The wavelength tuning element 48

reduces the bandwidth of the beam and can be used to match the wavelength of the laser to the absorption spectrum of the target to enhance the desired physiological effects. As the target cells and surrounding cells heat up, their respective absorption spectra change. In one embodiment,

the wavelength of each micropulse is changed to match the peak in the absorption spectrum of

the target cells. The tuning element 48 is in communication with a synchronizer 182 (FIG. 3)

and the synchronizer 182 transmits a series of trigger signals to the tuning element 48. In response to the trigger signals, the tuning element 48 adjusts the wavelength for each subsequent pulse in the spaced series of micropulses of laser radiation 104, 108, 112, 116.

A second mirror assembly 46 is partially transmissive, returning a portion of the

emanated light and allowing the remaining portion to exit the cell. The light resonates between

the first and second mirror assemblies 42, 46 and increases in intensity when lasing threshold is reached. At that point, a measurable amount of light passes through the second mirror assembly

46 as a pulsed output beam 50. The output beam 50, which is comprised of a spaced series of

micropulses of laser radiation 88, 92, 96, 100 (FIG. 2B), can be aimed at a cutaneous vascular

legion 60 (e.g., facial telangiectasia) of the patient 64 being treated.

FIG. 2A depicts a graph of the generated excitation pulses 104, 108, 112, 116. FIG.

2B depicts a graph of the output beam 50 corresponding to a series of micropulses 88, 92, 96, 100. The horizontal axes for both FIG. 2A and FIG. 2B represent time. The vertical axis of FIG. 2 A represents the electric current for driving the flashlamp; in this embodiment, current

measured in amperes. The vertical axis of FIG. 2B represents power of the output beam; in this

embodiment, power measured in watts.

The output beam 50 has an effective pulse duration 84 as shown in FIGS. 2 A and 2B. The effective pulse duration 84 is defined as the time from the start (i.e., rising edge) of the first

micropulse of laser radiation 88 to the end (i.e., falling edge) of the last micropulse of laser

radiation 100. Thus, the output beam 50 is not a continuous pulse of laser radiation, but a spaced

series of micropulses of laser radiation 88, 92, 96, 100. The number and amplitude of the excitation pulses 104, 108, 112, 1 16 determine the number and amplitude of micropulses of laser radiation 88, 92, 96, 100. The spacing between the micropulses of laser radiation 88, 92, 96, 100

does not necessarily have to be uniform. In other words, the spacing between the series of

excitation pulses 104, 108, 112, 116 can be varied in any way to accomplish the user's goals. Each excitation pulse 104, 108, 112, 116 (FIG. 2A) is formed using the pulse forming

networks 22 and the switching networks 26, as described in more detail below. In one

embodiment, each excitation pulse has more energy than the previous pulse in coordination with

an increasing lasing threshold 120. In other embodiments, the amplitude of each excitation pulse

104, 108, 112, 1 16 can vary as needed to accomplish various treatment goals. For example, in some cases, an excitation pulse will be higher or lower in amplitude than a subsequent pulse.

However, in general the amplitude of each excitation pulse is coordinated to be greater than the

increasing lasing threshold 120.

The increasing lasing threshold 120 is dependent on a variety of factors (as discussed

above). In general, the increase in lasing threshold 120 for a dye laser is proportional to the total

excitation energy delivered to the dye medium. This energy is, in turn, proportional to the

product of the excitation power and the excitation time duration. For a laser incorporating the

principles of the invention, the excitation time corresponds to the sum of the excitation times

124, 128, 132, 136 for each of the micropulses of laser radiation 88, 92, 96, 100. Because this sum is significantly shorter than the long effective pulse duration 84, the lasing threshold 120

increases slowly (i.e., smaller slope) relative to traditional continuous pulsed dye lasers.

In one exemplary embodiment, the laser 10 generates four pulses, each with a pulse

duration 124, 128, 132, 136 of 50 microseconds. Each pulse is spaced so that the time period from the start of the first pulse 88 until the end of the last pulse 100 (i.e., the long effective pulse

duration 84) is 10 milliseconds. This output beam has a long "effective" pulse duration (i.e., 10

milliseconds), but an actual total "on" time of only 200 microseconds.

The use of an output beam comprised of a series of micropulses not only helps improve the lasing threshold 120, but also makes the laser more energy efficient. The amount of

excitation energy converted to output pulse energy corresponds to the sum of the amount of - 10 - energy of each excitation pulse 104a, 108a, 112a, 116a above the lasing threshold 120. A known pulsed dye laser requires excitation energy throughout the entire pulse duration of the output

beam. None of the excitation energy below the lasing threshold 120 is converted to output laser

radiation. In contrast, the present invention requires excitation energy only when forming each

micropulse (i.e., no excitation energy is required between the excitation pulses 104, 108, 112,

116), except for the nominal simmer current 80. Thus, a laser incorporating the principles of the

invention requires less excitation pulse energy to deliver an output beam containing the same

amount of laser radiation energy as known pulsed dye lasers. Therefore, a laser incorporating the principles of the invention is more efficient.

FIG. 3 is a detailed representation of the pulse forming networks 22 and the switching

networks 26 used in the laser 10 to form the desired spaced series of excitation pulses 104, 108,

112, 116. The pulse forming networks 22 and the switching networks 26 have a plurality of

channels 150a, 150b, 150c, each channel corresponding to the creation of a single excitation

pulse. For example, channel one 150a corresponds to the first excitation pulse 104 (FIG. 2B),

channel two 150b corresponds to the second excitation pulse 108 (FIG. 2B) and channel n 150c

corresponds to the nth or last excitation pulse 116 (FIG. 2B).

In the pulse forming networks 22, each channel is a separate pulse forming network

and includes an energy storage element 160 (e.g., a capacitor) and an isolation element 164 (e.g., a diode). The storage element 160 is charged by the power supply 18 prior to the initiation of the

spaced series of excitation pulses 104, 108, 112, 116. In one embodiment, if the lasing threshold

120 increases, each subsequent excitation pulse needs to have a correspondingly higher amplitude. In another embodiment, each excitation can have a different amplitude dependent

upon the treatment procedure goals. To accomplish this, each storage element 160 has a different

value of capacitance such that a constant voltage from the power supply 18 stores different energies in each channel, as required to meet the treatment goals. In another embodiment, the power supply 18 is a programmable power supply and charges each energy storage element 160,

which are all the same value of capacitance, to different voltage levels. In a typical embodiment,

if the storage element is a capacitor, an inductive element (not shown) is positioned between the

pulse forming module 20 and the flashlamp 30.

The isolation element 164 provides protection from discharging a subsequent energy

storage element 160 into the power supply, when inhibited, or a previous energy storage element

160 that has previously discharged.

In the switching networks 26, each channel is a separate switching network and includes a switching element 168 (e.g., a SCR or IGBT, with the driving circuitry), a switch filter 172 (e.g., a snubber) and an isolation element 176 (e.g., a diode). The switching element 168

remains open, electrically disconnecting the energy storage element 160 of the same channel

from the flashlamp 30, while the energy storage element 160 is being charged by the power

supply 18. Upon receiving a trigger signal from a synchronizer 182, the switching element 168

closes, electrically connecting the energy storage element 160 to the flashlamp 30. The energy is

discharged from the energy storage element 160 of the same channel to the flashlamp 30 to create

a high intensity light pulse. The switch filter 172 maintains the energy flow to the flashlamp 30

and prevents ringing when the switching element 168 is closed. The isolation element 176 directs the current flow into the flashlamp 30 and prevents current from flowing into another

channel.

A synchronizer 182 synchronizes the closing of the switching elements 168a, 168b,

168c to create the desired spaced series of excitation pulses 104. 108, 116 (FIG. 2A) respectively.

Upon receiving a trigger input signal, the synchronizer 182 inhibits the power supply 18 and

closes the switching element 160a of channel one. The result is the creation of the first excitation pulse 104 (FIG. 2A). After a predetermined time delay, the synchronizer 182 closes

the switching element 168b of channel two, creating the second excitation pulse 108 (FIG. 2A).

This process is repeated until the predetermined number of excitation pulses in the spaced series

has been created. In another embodiment, the synchronizer 182 also communicates with the

tuning element 48. In coordination with the closing of each switching element 160, the synchronizer 182 sends a trigger signal to the tuning element to vary the wavelength of the

micropulse of laser radiation corresponding to the applicable excitation pulse.

One advantage of the present invention is that the flashlamp-excited dye laser, as

applied to selective photothermolysis, produces a beam of output pulses having a wavelength that

is more optimal than other lasers. By keeping the energy in each micropulse 88, 92, 96, 100

below the threshold for generating purpura, the output beam 50 of the present invention can be

used over a long effective pulse duration so that purpura is eliminated. In one embodiment, the parameters of pulse duration and fiuence level are chosen such that the laser can effectively treat facial telangiectasia while eliminating purpura. The pulse duration 124. 128, 132, 136 of each

micropulse is chosen to be greater than the thermal relaxation time of red blood cells and less

than the thermal relaxation time of the target vessel. The thermal relaxation time of red blood

cells is on the order of magnitude of 10 microseconds. By selecting the pulse duration 124, 128,

132, 136 of each micropulse to be longer than the thermal relaxation time of red blood cells, the

heat is dissipated to surrounding fluid thereby preventing the red blood cells from exploding.

Thus, the pulse duration 124, 128, 132, 136 is selected to be at least 10 microseconds.

Denaturing of the target vessel is desired, so the long effective pulse duration 84 should be less than the thermal relaxation time of the target vessel. The thermal relaxation time of the target vessel varies with its size. For most target vessels, an appropriate long effective pulse duration

84 should be less than 40 milliseconds. To be relatively benign to the epidermis and reduce epidermal injury, the long effective pulse duration 84 should be greater than the thermal

relaxation time of the epidermis (i.e., for the same reasoning as red blood cells). For most target

vessels, it is believed that an appropriate long effective pulse duration 84 should be greater than 5 milliseconds. Thus, a long effective pulse duration 84 between 5 and 40 milliseconds is chosen

for most target vessels.

In addition to the selection of the pulse duration, the time between micropulses is

optimized. The time between micropulses, the amplitude of the energy, and duration of each

micropulse affect the temperature profile of the target tissue. In known pulse lasers, the target

tissue temperature rises steadily throughout the laser pulse. In a laser of the present invention,

the temperature rise resembles discrete steps in temperature increase corresponding to each of the

micropulses. The spacing between each micropulse can be selected to optimize the thermal

profile for the greatest therapeutic efficacy. The spacing can also be optimized for combined use

with cooling devices (e.g., a dynamic cooling device) as described in more detail below.

The amount of energy delivered is another important parameter for effective treatment.

It is believed that to reduce or eliminate purpura, each single micropulse of laser energy should

have a fluence at the skin of less than about 5 j/cm". The entire fluence delivered to the skin

during the long effective pulse duration 84 (i.e., the sum of the fluence of each of the micropulses

88, 92, 96, 100) needs to exceed the minimum fluence level required for effective treatment. The effective therapeutic fluence necessary varies with the size of the target vessel and is, in general,

between 7 and 30 j/cm .

In one exemplary embodiment, the invention is programmed to generate, upon the

receipt of an input trigger signal, a spaced series of four micropulses of laser radiation 88, 92, 96,

100. Each micropulse has a pulse duration 124, 128, 132, 136 of 100 microseconds and a fluence of 3 j/cm" on target tissue. The series of micropulses 88, 92, 96, 100 are spaced so that from the start (i.e., rising edge) of the first micropulse 88 to the end (i.e., falling edge) of the last micropulse 100 is 10 milliseconds. As a result, the output beam delivers a fluence of 12 j/cm at

the skin over an effective pulse duration 84 of 10 milliseconds.

In another exemplary embodiment, dynamic cooling of the epidermal layers of the

skin occurs between each micropulse of laser radiation 88, 92, 96, 100. The cooling system may comprise a pressurized container of a low boiling point fluid. Cooling of the surface of the skin

is accomplished by briefly spraying the skin with the fluid, which extracts heat from the skin on contact. The fluid extracts heat from the surface skin by the virtue of evaporative cooling. The

fluid is sprayed on the skin between each micropulse of laser radiation. By spraying between the

micropulses of the laser, scattering of the laser beam by the spray is avoided. The energy in each micropulse can be adjusted to the amount of cooling fluid applied prior to the micropulse. The

combination of timing and cooling can be varied in any way to accomplish the treatment goals. In

one embodiment, with a long period of cooling prior to the first micropulse 88, the first

micropulse 88 can contain a higher energy level than the subsequent micropulses 92, 96, 100. In

another embodiment, the first two micropulses 88, 92 are produced, the skin is cooled for a

relatively long period (e.g., 5 milliseconds), and a third micropulse 96 is applied with a much higher amount of energy corresponding to the amount of cooling.

Experimental Results

A number of patients were treated to verify the benefits of the invention. Eleven adults

(age eighteen or above) with Fitzpatrick skin types I-III and facial telangiectasias were used for

the study. Two distinct areas of telangiectasias were identified on the faces of these volunteers. Pretreatment photographs were taken. One area was treated with the Candela SPTL lb, a

flashlamp pulsed dye laser with a wavelength of 589 ± 2 nm and pulse duration of 450 μsec,

currently in use for treatment of vascular lesions. A second area was treated with a laser incorporating the principles of the invention. The laser generated an output beam having the same wavelength and an effective pulse duration of 20 msec.

Photographs were taken and/or assessments were made immediately after the procedure

as well as 1 day, 4 days, 7 days, 14 days and 2 months post-procedure. At each of these time periods, the principal investigator evaluated the lesions on an analog scale for purpura/erythema

and resolution of the vessel. Any evidence of hyperpigmentation, hypopigmentation, crusting, or

skin textural change was also noted.

Evaluators compared the photos and/or assessments of treatments with the lasers

described above of the 20 msec pulse duration and the 450 μsec pulse duration. The clearance performance (removal of the facial telangiectasias) was equivalent between the two lasers. The

laser of the present invention demonstrated improved performance over the SPTL-Ib with regards

to the occurrence and severity of purpura, pain and other side effects. A similar experiment was

performed using a 10 millisecond long effective pulse and the results were the same.

Equivalents

The invention may be embodied in other specific forms without departing from the

spirit or essential characteristics thereof. The foregoing embodiments are therefore to be

considered in all respects illustrative rather than limiting on the invention described herein.

Scope of the invention is thus indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein.

Claims

CLAIMS 1. A method of generating a pulsed output beam of laser radiation having a long effective

pulse duration in a flashlamp-excited dye laser, the method comprising:

a) generating electronically a spaced series of excitation pulses; b) driving the flashlamp-excited dye laser with the series of excitation pulses;

and c) producing an output beam comprised of a series of micropulses of laser

radiation.

2. The method of claim 1 wherein each pulse within the spaced series of excitation pulses

has an increasing amplitude in coordination with an increasing lasing threshold for the

flashlamp-excited dye laser. 3. The method of claim 1 further comprising adjusting a tuning element in coordination with

each pulse within the spaced series of excitation pulses to vary the wavelength of each micropulse.

4. The method of claim 1 wherein the effective pulse duration of the output beam is at least

5 milliseconds. 5. The method of claim 1 wherein each micropulse has a pulse duration of at least 10

microseconds.

6. The method of claim 1 wherein each micropulse has an energy level less than half of the

total energy of the series of micropulses. 7. The method of claim 1 wherein the series of micropulses has a total energy greater than 1 Joule. 8. The method of claim 1 further comprising directing the output beam of laser radiation at a cutaneous vascular lesion.

. A method of generating a pulsed output beam of laser radiation having a long effective

pulse duration in a flashlamp-excited laser, the method comprising:

a) generating electronically a series of spaced excitation pulses;

b) driving a flashlamp with the series of spaced excitation pulses to produce a series of light pulses; c) directing the series of light pulses to a lasing medium; and d) producing from the lasing medium an output laser beam comprised of a

series of spaced micropulses of laser radiation which, in combination, have a long effective pulse duration.

10. The method of claim 9 wherein each excitation pulse has an increasing amplitude in coordination with an increasing lasing threshold for the flashlamp-excited laser.

1 1. The method of claim 9 further comprising adjusting a tuning element in coordination with

each pulse within the spaced series of excitation pulses to vary the wavelength of each

micropulse.

12. The method of claim 9 wherein lasing medium comprises a dye mixture suspended in a liquid. 13. The method of claim 9 wherein the effective pulse duration of the output beam is at least

5 milliseconds. 14. The method of claim 9 wherein each micropulse has a pulse duration of at least 10

microseconds. 15. The method of claim 9 wherein each micropulse has an energy level less than half of the

total energy of the series of micropulses. 16. The method of claim 9 wherein the series of micropulses has a total energy greater than 1 Joule.

17. The method of claim 9 further comprising directing the output beam of laser radiation at a cutaneous vascular lesion.

18. The method of claim 9 further comprising directing the output beam of laser radiation at a metallic or non-metallic target.

19. A method of treating a cutaneous vascular lesion with a flashlamp-excited dye laser, the method comprising:

a) generating electronically a spaced series of excitation pulses; b) driving the flashlamp-excited dye laser with the series of excitation pulses; and

c) producing an output beam comprised of a series of micropulses of laser

radiation;

d) directing the output beam of laser radiation at the cutaneous vascular lesion.

20. The method of claim 19 wherein the pulse parameters of each micropulse are selected to

minimize the formation of purpura.

21. The method of claim 19 further comprising adjusting a tuning element in coordination with each pulse within the spaced series of excitation pulses to vary the wavelength of each micropulse. 22. The method of claim 19 wherein the effective pulse duration of the output beam is

between about 5 milliseconds and about 40 milliseconds.

23. The method of claim 19 wherein each micropulse has a pulse duration of at least 10

microseconds. 24. The method of claim 19 wherein each micropulse delivered to the skin has a fluence less than 5 j/cm².

25. The method of claim 19 wherein the series of micropulses delivered to the skin has a total fluence greater than 6 j/cm².

26. A flashlamp-excited dye laser for producing a pulsed output beam of laser radiation having a long effective pulse duration, comprising:

a pulse forming module for generating in response to a trigger signal a series of spaced excitation pulses;

a flashlamp electrically receiving the series of spaced excitation pulses from the pulse

forming module, the flashlamp producing a series of light pulses in response thereto; and

a liquid dye medium receiving the series of light pulses from the flashlamp and, in response thereto, producing an output laser beam comprised of a series of spaced micropulses of laser radiation which, in combination, have a long effective pulse duration.

27. The flashlamp-excited dye laser of claim 26 wherein each pulse within the spaced series of excitation pulses is generated with increasing amplitude in coordination with an

increasing lasing threshold for the flashlamp-excited dye laser. 28. The flashlamp-excited dye laser of claim 26 further comprising a tuning element for

varying the wavelength of each micropulse in response to a trigger signal for a series of

spaced excitation pulses.

29. The flashlamp-excited dye laser of claim 26 wherein the effective pulse duration of the output beam is at least 5 milliseconds. 30. The flashlamp-excited dye laser of claim 26 wherein each micropulse of laser radiation in the produced series has a pulse duration of at least 10 microseconds.

31. The flashlamp-excited dye laser of claim 26 wherein each micropulse has an energy level

less than half of the total energy of the series of micropulses.

32. The flashlamp-excited dye laser of claim 26 wherein the series of micropulses has a total energy greater than 1 Joule.

33. The flashlamp-excited dye laser of claim 26 wherein the flashlamp-excited dye laser is used to treat a cutaneous vascular lesion.