WO2001008545A2 - Thermal quenching of tissue - Google Patents

Thermal quenching of tissue Download PDF

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Publication number
WO2001008545A2
WO2001008545A2 PCT/US2000/020311 US0020311W WO0108545A2 WO 2001008545 A2 WO2001008545 A2 WO 2001008545A2 US 0020311 W US0020311 W US 0020311W WO 0108545 A2 WO0108545 A2 WO 0108545A2
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WO
WIPO (PCT)
Prior art keywords
tissue
structures
coolmg
treatment
target tissue
Prior art date
Application number
PCT/US2000/020311
Other languages
French (fr)
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WO2001008545A3 (en
Inventor
Dale E. Koop
Jonathan M. Baumgardner
Robert A. Weiss
Original Assignee
Laser Aesthetics, Inc.
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Application filed by Laser Aesthetics, Inc. filed Critical Laser Aesthetics, Inc.
Priority to DE10082526T priority Critical patent/DE10082526T1/en
Priority to AU66089/00A priority patent/AU6608900A/en
Publication of WO2001008545A2 publication Critical patent/WO2001008545A2/en
Publication of WO2001008545A3 publication Critical patent/WO2001008545A3/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/203—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser applying laser energy to the outside of the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00041—Heating, e.g. defrosting
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00452—Skin

Definitions

  • This invention is related delivery of laser or other source of thermal energy to biological or other tissue for treatment therein, and more particularly, to a method and system for delivery of the laser or other source of thermal energy to the target tissue wherein surroundmg tissue, mcluding surface tissue, is also elevated m temperature by conduction of heat from the target tissue, and wherein thermal quenching of the surroundmg tissue, and in particular the surface tissue, prevents thermal damage thereto
  • a selected structure m tissue such as a vem or hair follicle
  • causmg heat affected changes m tissue adjacent to the selected structure The p ⁇ or art treatments use a method called selective photothermalysis, whereby laser or pulsed light source is tuned to a wavelength whereby its energy is preferentially absorbed by a preselected target
  • the energy from the source is delivered within a time pe ⁇ od short enough for heat to build up in the target and faster than it flows mto adjacent regions by thermal conduction
  • the amount of energy or fluence delivered to the target is chosen such that the temperature ⁇ se in the targeted region results m an mtended thermal treatment of the target
  • Vascular lesions have been treated for more than twenty years with a variety of lasers and light sources including pulsed dye lasers, argon lasers. Nd YAG lasers, and flashlamps
  • pulsed dye laser operating at a wavelength of 577 nanometers is very effective since it can penetrate through skin and is absorbed by hemoglobm m small vems resulting in heat build up and a photo- coagulation of the vem
  • the energy is confined to a short tune pe ⁇ od. less than the thermal relaxation time of the vessel being treated, so that heat loss to surroundmg tissue is minimized du ⁇ ng treatment
  • the principal is known as. or at least has been characte ⁇ zed as. selective photothermalysis Selective Photothermalvsis. Anderson, R R . Par ⁇ sh. J A , Science 1983 Vol 220
  • the pulsed dye laser is useful for many smaller vessels, m lesions such as port wine stains, the larger and deeper lying vessels found m leg telangiactasias and other undesirable lesions are difficult to treat
  • the pulsed dye laser energy is absorbed too strongly by hemogolobin and so does not penetrate fully though larger vems which approach diameters of 0 1 mm to 3 mm m diameter Larger vessels also require more energy to achieve the same coagulative effect and have longer thermal relaxation tunes
  • a va ⁇ ety of lasers and a non-coherent intense light source with tunable wavelength have all been used to treat vessels of different sizes and depths m skin
  • va ⁇ ous cooling methods are that a greater fluence can be used to treat vessels without significant thermal damage du ⁇ ng treatment to the epidermis. Avoiding epidermal damage is extremely important for the treatment of deeper and larger vessels smce the fluences and wavelengths used could cause substantial damage to uncooled epidermis.
  • Problems associated with the p ⁇ or art include the subsequent conduc ⁇ on of heat away from the treated vessels or other target tissue mto adjacent tissue. For larger vessels, a significant amount of heat builds up du ⁇ ng the treatment. The treated vessels cool off by thermal conduction to su ⁇ oundmg tissue. The temperature of the tissue adjacent to the vessel will nse immediately after treatment and may reach levels causing significant patient discomfort and even epidermal damage.
  • the system for generatmg light energy is a laser system such as but not limited to a solid-state laser, including but not limited to a neodymium-doped ytt ⁇ um- aluminum-garnet (Nd YAG) laser
  • the system for generatmg light energy is a gas discharge flashlamp or an incandescent-type filament lamp
  • the energy from the generatmg system may be directed mto or coupled to a delivery device such as but not limited to a fiber optic or articulated arm for transrmtting the hght energy to the target tissue
  • the light energy may be focused on tissue with a focusmg lens or system of lenses
  • the surface of the tissue may be cooled with a coolmg device including but not limited to an lr ⁇ gating solution, a spray or flow of refrigerant or other crvogemc mate ⁇ al, or a transparent window cooled by other active means, or other dynamic or passive coolmg means
  • the tissue may be preheated with a heatmg device such as, but not limited to an mtense light source, a flashlamp. a filament lamp, laser diode, other laser source, elect ⁇ cal current, or other electromagnetic or mechanical energy which penetrates mto layers of tissue beneath the surface
  • the preheatmg can occur simultaneously or just p ⁇ or to the surface coolmg of ⁇ ssue from the coolmg device such that the tissue preheating results in a temperature ⁇ se m underlying layers of tissue, and a temperature profile results
  • the pulsed application of energy from the energy delivery device results m a temperature profile that preferentiallv heats a selected structure or target in tissue, arid the post coolmg prevents thermal damage to tissue adjacent to that structure Tins also reduces the overall pulse energy level needed of the pulsed treatment device due to the fact that a desirable temperature profile exists p ⁇ or to delivery of the pulsed treatment energy
  • the tissue may be post cooled with a dynamic coolmg device such as. but not limited to a pulse, spray or other flow of refrigerant such that the post coolmg occurs after a temperature ⁇ se m an underlying targeted structure and a temperature profile results such that the pulsed application of energy from the energy delivery device results m a temperature profile that preferential heats a selected structure m tissue without subsequent undesirable heatmg to tissue adjacent to that structure from thermal conduction
  • a dynamic coolmg device such as. but not limited to a pulse, spray or other flow of refrigerant such that the post coolmg occurs after a temperature ⁇ se m an underlying targeted structure and a temperature profile results such that the pulsed application of energy from the energy delivery device results m a temperature profile that preferential heats a selected structure m tissue without subsequent undesirable heatmg to tissue adjacent to that structure from thermal conduction
  • FIG 1 is a representative schematic block diagram of a preferred embodiment of a system for thermal quenching of tissue of the present mvention
  • FIG 2 is a more detailed representative schematic block diagram of a prefe ⁇ ed embodiment of the delivery device shown m FIG 1 of the present mvention
  • FIG 3 is a representative sample data plot of the temperature of surface tissue and target tissue achieved by methods and systems of the p ⁇ or art having precoolmg
  • FIG 4 is a representative sample data plot of the temperature of surface tissue and target ⁇ ssue achieved by a preferred embodiment of the method and system of the present invention such as shown in FIGS 1 and 2 having precoolmg
  • FIG 5 is a representative sample data plot of the temperature of surface tissue and target ussue achieved by a preferred embodiment of the method and system of the present mvention such as shown m FIGS 1 and 2 without precoolmg
  • FIG 1 is a representative schematic block diagram of a prefe ⁇ ed embodiment of a system 100 for thermal quenching of tissue of the present mvention Operation of energy source 102 to produce energy for delivery by the system 100 is controlled according to control signal 104 from control system 106
  • Control system 106 mcludes a physician interface 108 for operating the system
  • Said interface 108 optionally mcludes a footswitch for energy delivery, display and interacuve and/or menu d ⁇ ven operation utilizing operator input, prompts, etc
  • Additional energy delivery control interface means shall be known to those skilled in the art
  • energy source 102 is a neodymium doped yttnum-aluminum- garnet (Nd YAG) laser, energized by a flash-lamp or laser diode
  • Energy source 102 is controlled by control system 106 which comp ⁇ ses the software and electronics to momtor and control the laser system, and interface 108
  • the beam of laser energy 110 from the energy source 102 is directed mto a delivery device 112 which may be an optical fiber, a fiber bundle or articulated arm, etc
  • Modem instruments to provide dynamic coolmg of the surface layers of fissue or other mate ⁇ als are well suited to these applications
  • a coolant spray can be provided through a handpiece or it could be provided with another separate device
  • a connection to a computer and the control system 106 of the energy source 102 will allow the system 100 to utilize electronic or other thermal sensmg means and obtain feedback control signals for the handpiece
  • An optimum coolmg strategy might be one that uses a post-irradiation coolmg spur
  • the distance between the aperture of the spray valve and the skin surface should be maintained at about 20 millimeters
  • the target tissue upon delivery of laser energy onto the surface and therethrough, the target tissue will be raised to the optimal treatment temperature and generally not any higher, m an adequately rapid process, with the surface temperature of the skin remaining at a temperature below the threshold for damage temperature
  • the threshold for damage temperature is the temperature below which the skin or other Ussue can be elevated without causmg temporary or permanent thermal damage, and above which the Ussue may undergo either transient or long term thermally mduced physiological change
  • the wavelength of irradiated light energy is selectively absorbed by hemoglobm or hair follicles, or other tissue with pigmentation or chromophores of a certain type, but passes through the surface and overlying/adjacent tissue to the target tissue with minimal absorption
  • the wavelength of irradiated light energy is selectively absorbed by hemoglobm or hair follicles, or other tissue with pigmentation or chromophores of a
  • a passive heat sink mcludes glass or sapphire tip probes, and other types of devices to lay on the surface of the skin
  • a dynamic type of heat sink will refer to those actively cooled by flowing gas or liquid, jets or spurts of coolant such as freon, and other active types of heat exchangers suitable for surface coolmg while rrradiating sub-surface portions of collagen tissue
  • U S Patent No 5,820.626 issued Oct 13. 1998 to Baumgardner and U S Application Se ⁇ al No 08/938.923 filed Sep 26, 1 97 by Baumgardner et al . both inco ⁇ orated herem by reference in their entireties teach a coolmg laser handpiece with refillable coolant reservoir, and can be utilized as a handpiece for de verv device 112 and heat sink 114
  • FIG 2 is a more detailed representative schematic block diagram of a preferred embodiment of the delivery device 112 shown m FIG 1 of the present mvention.
  • the energy from the energy source 102 is directed mto delivery device 112 via a delivery channel 130 which may be a fiber optic, articulated arm, or an electrical cable etc
  • a delivery channel 130 which may be a fiber optic, articulated arm, or an electrical cable etc
  • a nozzle 134 is useful for directing coolant from reservoir 135 to the tissue 118, and a valve 136 for controlling the coolant mterval
  • a temperature sensor 137 may be used to momtor the temperature ⁇ se of the target tissue 118
  • Control system 106 monitors the temperature signal from sensor 137 and controls valve 136 and energy source 102
  • Reservoir 135 may be m the delivery device 112 or elsewhere, and contains a refrigerant which may be applied to surface tissue 120 by spraying said refrigerant from coolmg nozzle 124 in
  • the temperature of the surface tissue 116 as well as the target tissue 120 are at T s and T, respectively It will be understood that typically the skin surface is at a temperature somewhat below actual body temperature Typically, this range might be between about 28 and about 34 degrees Celsius Furthermore, a target vem. hair follicle or other structure can be assumed to be at about or somewhat just below 37 degrees Celsius, or actual body temperature
  • T s drops to a level determined by the length of time 244 for which the surface tissue 120 is exposed to the coolant.
  • time pe ⁇ ods of about 30 milliseconds.
  • T s may drop from a typical temperature of about 32 degrees Celsius to just above 0 degrees Celsius
  • a short delay 245 following delivery of refrigerant may be used, and is typically between 0 and 100 milliseconds. This allows tune for coolmg of at least a layer of epidermis to a depth of 50 to 250 micrometers
  • the pulsed energy is applied over predetermmed or other time pe ⁇ od 246
  • the time pe ⁇ od 246 depends on the size of the target and the fluence delivered, as indicated by principles of selective photothermalysis For example, m experiments with an Nd YAG laser operatmg at 1064 nanometers, one application of a 10 millisecond pe ⁇ od and a fluence of 50 joules per square centimeter was sufficient to treat
  • the target tissue 116 cools by conduction of thermal energy to adjacent overlaying tissue 118 including the surface tissue 116. with a resultant temperature ⁇ se m the target tissue 120 dependant on the size and depth of the target tissue 120 As T, equalizes with su ⁇ oundmg tissue, the T s may ⁇ se above the level of patient discomfort and even cause damage to surface tissue 116
  • FIG 3 is a representative sample data plot of the temperature of surface tissue 116 and target tissue 120 achieved by methods and systems of the p ⁇ or art having precoolmg
  • FIG 4 is a representative sample data plot of the temperature of surface tissue 116 and target tissue 120 achieved by a prefe ⁇ ed embodiment of the method and system of the present mvention such as shown m FIGS 1 and 2 having precoolmg
  • the method of the present mvention mcludes the process of precoolmg surface tissue 116 and target tissue 120 slightly, followed by a short tune pe ⁇ od 245 and subsequent delivery of thermal energy to the body du ⁇ ng time pe ⁇ od 246 such as shown m FIG 3
  • refrigerant is also applied subsequent to the energy pulse by opening valve 136 as desired or as indicated, thus keepmg T s below the threshold for damage temperature 250
  • FIG 4 shows a pulse of coolant applied du ⁇ ng tune pe ⁇ od 248 which is subsequent to the application of pulsed energy du ⁇ ng pe ⁇ od 246 This results m thermal quenching of the surface tissue 116
  • the thermal quenching pulse or other flow of refrigerant or other means for coolmg is applied after the beginning of treatment pe ⁇ o
  • crvogemc fluid was applied to the surface tissue 116 within 10 milliseconds of the end of the energy pulse of tune pe ⁇ od 246 and for a duration 248 of 20 milliseconds.
  • the pe ⁇ od of thermal quenching 248 preferably 10 milliseconds to 30 milliseconds immediately after the treatment energy This sequence significantly reduced patient discomfort compared to treatment with out thermal quenchmg
  • the effect of thermal quenchmg is not dependant on pre-coolmg and may be used as the only method of coolmg m many cases.
  • FIG. 5 is a representative sample data plot of the temperature of surface tissue and target tissue achieved by a prefe ⁇ ed embodiment of the method and system of the present invention such as shown m FIGS. 1 and 2 without precooling.
  • the thermal quenchmg pulse or other flow of refrigerant or other means for cooling over tune pe ⁇ od 248 is applied after the beginning of treatment pe ⁇ od 246 and may be initiated before or after the end of time pe ⁇ od 246. It is important that the peak or highest temperature of the surface tissue 116 never ⁇ se above the threshold for damage temperature 250.
  • the present invention requires less cooling of the target tissue, structure or area du ⁇ ng the treatment phase than is typically required, resultmg m more efficient heatmg of the selected target and less thermal damage to surrounding tissue.
  • re-heating of tissue can be useful.
  • U.S. Application Serial No. 09/185.490 filed Nov. 3, 1998 by Koop et al. teaches methods and systems for performing subsurface heatmg of mate ⁇ al and in inco ⁇ orated herem by reference in its entirety. In these methods, target or subsurface tissue is preheated to an elevated, non-destructive temperature which is somewhat below that of treatment.
  • the temperature of the target tissue or structures is raised to treatment temperature
  • the target tissue or structures will conduct heat mto the body, especially to adjacent tissue and surface tissue, at which tune the post-coolmg of the present mvention can be mitiated so as to prevent damage to adjacent tissue or derrms or other surface tissue

Abstract

A method and device (100) for selective heating of subsurface structures in material such as tissue (120) include a cooling device (114) for thermally quenching or removing heat from the top surface of tissue (120) during or just after delivering pulsed energy (110) to target or subsurface structures or tissue (120), a preferred embodiment of the invention using dynamic cooling, to quench the thermal energy conducted from the targeted structure into surrounding tissue (118).

Description

IN THE UNITED STATES RECEΓVTNG OFFICE INTERNATIONAL PATENT (PCT) APPLICATION
Title: THERMAL QUENCHING OF TISSUE
FIELD OF THE INVENTION This invention is related delivery of laser or other source of thermal energy to biological or other tissue for treatment therein, and more particularly, to a method and system for delivery of the laser or other source of thermal energy to the target tissue wherein surroundmg tissue, mcluding surface tissue, is also elevated m temperature by conduction of heat from the target tissue, and wherein thermal quenching of the surroundmg tissue, and in particular the surface tissue, prevents thermal damage thereto
BACKGROUND OF THE INVENTION
It is sometimes desirable to cause heat affected changes m a selected structure m tissue, such as a vem or hair follicle, without causmg heat affected changes m tissue adjacent to the selected structure The pπor art treatments use a method called selective photothermalysis, whereby laser or pulsed light source is tuned to a wavelength whereby its energy is preferentially absorbed by a preselected target The energy from the source is delivered within a time peπod short enough for heat to build up in the target and faster than it flows mto adjacent regions by thermal conduction The amount of energy or fluence delivered to the target is chosen such that the temperature πse in the targeted region results m an mtended thermal treatment of the target
Vascular lesions have been treated for more than twenty years with a variety of lasers and light sources including pulsed dye lasers, argon lasers. Nd YAG lasers, and flashlamps The pulsed dye laser operating at a wavelength of 577 nanometers is very effective since it can penetrate through skin and is absorbed by hemoglobm m small vems resulting in heat build up and a photo- coagulation of the vem The energy is confined to a short tune peπod. less than the thermal relaxation time of the vessel being treated, so that heat loss to surroundmg tissue is minimized duπng treatment The principal is known as. or at least has been characteπzed as. selective photothermalysis Selective Photothermalvsis. Anderson, R R . Parπsh. J A , Science 1983 Vol 220
Pages 524-
Although the pulsed dye laser is useful for many smaller vessels, m lesions such as port wine stains, the larger and deeper lying vessels found m leg telangiactasias and other undesirable lesions are difficult to treat The pulsed dye laser energy is absorbed too strongly by hemogolobin and so does not penetrate fully though larger vems which approach diameters of 0 1 mm to 3 mm m diameter Larger vessels also require more energy to achieve the same coagulative effect and have longer thermal relaxation tunes A vaπety of lasers and a non-coherent intense light source with tunable wavelength have all been used to treat vessels of different sizes and depths m skin
Melanin absorption of laser energy results m some heatmg of the epidermis by each of the vaπous energy sources used for vascular treatment Several methods have been descπbed for coolmg the surface of skin duπng treatment to minimize the πsk of thermal injury to tissue adjacent to the targeted vems One early method mcluded pre-coo ng with ice for several minute pπor to treatment
U S Patent 5.282,797 issued Feb 1, 1994 to Chess descπbes a method of circulating coolmg fluid over a transparent plate in contact with the treatment area to cool the epidermis duπng treatment
U S Patent 5,344.418 issued Sep 6. 1994 to Ghaffaπ descπbes a method whereby a coolant is used for a predetermined time interval m coordrnaϋon with the delivery of laser energy to optimize the coolmg of the epidermis and rrunimize coolmg of the targeted vessel U S Patent 5,814,040 issued Sep 29. 1998 to Nelson et al descπbes a dynamic coolmg method whereby a cryogenic spurt is applied for a predetermined short time directly onto the skin m the target region. The time peπod is well controlled and limited so that coolmg is confined only to the epidermis while leaving the temperature of deeper port wine stains substantially unchanged.
The result of the vaπous cooling methods is that a greater fluence can be used to treat vessels without significant thermal damage duπng treatment to the epidermis. Avoiding epidermal damage is extremely important for the treatment of deeper and larger vessels smce the fluences and wavelengths used could cause substantial damage to uncooled epidermis.
Problems associated with the pπor art include the subsequent conducϋon of heat away from the treated vessels or other target tissue mto adjacent tissue. For larger vessels, a significant amount of heat builds up duπng the treatment. The treated vessels cool off by thermal conduction to suπoundmg tissue. The temperature of the tissue adjacent to the vessel will nse immediately after treatment and may reach levels causing significant patient discomfort and even epidermal damage.
Therefore what is needed is a method and device which subsequently cools and quenches heat build up in tissue, and especially in surface tissue, adjacent to tissue or structures treated in the thermally-mediated process or treatment.
ADVANTAGES AND SUMMARY OF THE INVENTION It is therefore an advantage and an object of the present invention to provide an improved system for selectively cooling tissue during photothermal treatment. It is a further advantage of the present mvention to provide such a system which uses dynamic cooling to quench heat build up during and after photothermal treatment.
It is a further advantage of the present invention to provide such a system which selectively heats a subsurface structure m tissue and subsequently quenches heat build up in non-target tissue. It is a further advantage of the present mvention to reduce the level of pulsed energy needed for treatment by rrunimizing precooling of the tissue.
It is a further advantage of the present invention to provide such a system which selectively heats a subsurface structure m skin to cause thermal affected changes m said subsurface structure without significant epitne al damage due to subsequent heatmg from the target region
It is a further advantage of the present mvention to provide such a system which selectively heats vascular lesions m tissue and quenches subsequent heat build up m epithelial tissue It is a further advantage of the present mvention to provide such a system which selectively heats hair follicles m tissue and quenches subsequent heat build up m epithelial tissue
It is a further advantage of the present mvention to require less coolmg of the target area than is typically required, resultmg m more efficient heatmg of the selected target and less thermal damage to surroundmg tissue In a prefeπed embodiment, the system for generatmg light energy is a laser system such as but not limited to a solid-state laser, including but not limited to a neodymium-doped yttπum- aluminum-garnet (Nd YAG) laser
In additional preferred embodiments, the system for generatmg light energy is a gas discharge flashlamp or an incandescent-type filament lamp The energy from the generatmg system may be directed mto or coupled to a delivery device such as but not limited to a fiber optic or articulated arm for transrmtting the hght energy to the target tissue
The light energy may be focused on tissue with a focusmg lens or system of lenses
The surface of the tissue may be cooled with a coolmg device including but not limited to an lrπgating solution, a spray or flow of refrigerant or other crvogemc mateπal, or a transparent window cooled by other active means, or other dynamic or passive coolmg means
The tissue may be preheated with a heatmg device such as, but not limited to an mtense light source, a flashlamp. a filament lamp, laser diode, other laser source, electπcal current, or other electromagnetic or mechanical energy which penetrates mto layers of tissue beneath the surface The preheatmg can occur simultaneously or just pπor to the surface coolmg of ϋssue from the coolmg device such that the tissue preheating results in a temperature πse m underlying layers of tissue, and a temperature profile results The pulsed application of energy from the energy delivery device results m a temperature profile that preferentiallv heats a selected structure or target in tissue, arid the post coolmg prevents thermal damage to tissue adjacent to that structure Tins also reduces the overall pulse energy level needed of the pulsed treatment device due to the fact that a desirable temperature profile exists pπor to delivery of the pulsed treatment energy
The tissue may be post cooled with a dynamic coolmg device such as. but not limited to a pulse, spray or other flow of refrigerant such that the post coolmg occurs after a temperature πse m an underlying targeted structure and a temperature profile results such that the pulsed application of energy from the energy delivery device results m a temperature profile that preferential heats a selected structure m tissue without subsequent undesirable heatmg to tissue adjacent to that structure from thermal conduction
Numerous other advantages and features of the present mvention will become readily apparent from the following detailed descπption of the mvention and the embodiments thereof, from the claims and from the accompanying drawings
BRIEF DESCRIPTION OF THE DRAWINGS FIG 1 is a representative schematic block diagram of a preferred embodiment of a system for thermal quenching of tissue of the present mvention
FIG 2 is a more detailed representative schematic block diagram of a prefeπed embodiment of the delivery device shown m FIG 1 of the present mvention
FIG 3 is a representative sample data plot of the temperature of surface tissue and target tissue achieved by methods and systems of the pπor art having precoolmg
FIG 4 is a representative sample data plot of the temperature of surface tissue and target ϋssue achieved by a preferred embodiment of the method and system of the present invention such as shown in FIGS 1 and 2 having precoolmg
FIG 5 is a representative sample data plot of the temperature of surface tissue and target ussue achieved by a preferred embodiment of the method and system of the present mvention such as shown m FIGS 1 and 2 without precoolmg
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT The descπption that follows is presented to enable one skilled m the art to make and use the present mvention, and is provided m the context of a particular application and its requirements Vaπous modifications to the disclosed embodiments will be apparent to those skilled m the art, and the general principals discussed below may be applied to other embodiments and applications without departing from the scope and spiπt of the invention Therefore, the mvention is not mtended to be limited to the embodiments disclosed, but the mvention is to be given the largest possible scope which is consistent with the principals and features descπbed here
FIG 1 is a representative schematic block diagram of a prefeπed embodiment of a system 100 for thermal quenching of tissue of the present mvention Operation of energy source 102 to produce energy for delivery by the system 100 is controlled according to control signal 104 from control system 106 Control system 106 mcludes a physician interface 108 for operating the system Said interface 108 optionally mcludes a footswitch for energy delivery, display and interacuve and/or menu dπven operation utilizing operator input, prompts, etc Additional energy delivery control interface means shall be known to those skilled in the art
In a preferred embodiment, energy source 102 is a neodymium doped yttnum-aluminum- garnet (Nd YAG) laser, energized by a flash-lamp or laser diode Energy source 102 is controlled by control system 106 which compπses the software and electronics to momtor and control the laser system, and interface 108 The beam of laser energy 110 from the energy source 102 is directed mto a delivery device 112 which may be an optical fiber, a fiber bundle or articulated arm, etc Modem instruments to provide dynamic coolmg of the surface layers of fissue or other mateπals are well suited to these applications A coolant spray can be provided through a handpiece or it could be provided with another separate device Finally, a connection to a computer and the control system 106 of the energy source 102 will allow the system 100 to utilize electronic or other thermal sensmg means and obtain feedback control signals for the handpiece An optimum coolmg strategy might be one that uses a post-irradiation coolmg spurt that provides coolmg or dissipation of the epidermal heat generated bv absorption of energy m the non-isotropic skin, optionally containing vaπous pigmentation levels An appropπate cryogen spray would be liquid mtrogen or tetrafluoroethane. C2H2F4, an environmentally compatible, non-toxic, non-flammable freon substitute In clinical application the distance between the aperture of the spray valve and the skin surface should be maintained at about 20 millimeters In a preferred embodiment of the present mvention. upon delivery of laser energy onto the surface and therethrough, the target tissue will be raised to the optimal treatment temperature and generally not any higher, m an adequately rapid process, with the surface temperature of the skin remaining at a temperature below the threshold for damage temperature It will be understood that the threshold for damage temperature is the temperature below which the skin or other Ussue can be elevated without causmg temporary or permanent thermal damage, and above which the Ussue may undergo either transient or long term thermally mduced physiological change As descπbed, the wavelength of irradiated light energy is selectively absorbed by hemoglobm or hair follicles, or other tissue with pigmentation or chromophores of a certain type, but passes through the surface and overlying/adjacent tissue to the target tissue with minimal absorption However, once the target tissue or structure becomes elevated m temperature, surrounding and adjacent tissue will become hot due to conduction of heat from the target tissue or structures Post-irradiation coolmg can then be initiated, and tissue other than the target tissue is prevented from mcreasmg m temperature beyond the threshold of damage or adverse effect Adverse effects of elevated tissue surface temperature mclude discomfort or pain, thermal denaturing of proteins and necrosis of individual cells at the surface only, or deeper tissue ablation potentially leadmg to hypeφlasia, scarring, or hyperpigmentation, a proliferation of cells formed m response to the mduced trauma. In a preferred embodiment of the method of the present mvention. heatmg and subsequent post-cooling are performed m a predetermined timing sequence, optionally with the use of tuner circuits and/or other controller means
Thus, it will be obvious to those skilled in the art that a passive heat sink mcludes glass or sapphire tip probes, and other types of devices to lay on the surface of the skin It will also be obvious that a dynamic type of heat sink will refer to those actively cooled by flowing gas or liquid, jets or spurts of coolant such as freon, and other active types of heat exchangers suitable for surface coolmg while rrradiating sub-surface portions of collagen tissue U S Patent No 5,820.626 issued Oct 13. 1998 to Baumgardner and U S Application Seπal No 08/938.923 filed Sep 26, 1 97 by Baumgardner et al . both incoφorated herem by reference in their entireties, teach a coolmg laser handpiece with refillable coolant reservoir, and can be utilized as a handpiece for de verv device 112 and heat sink 114
FIG 2 is a more detailed representative schematic block diagram of a preferred embodiment of the delivery device 112 shown m FIG 1 of the present mvention. The energy from the energy source 102 is directed mto delivery device 112 via a delivery channel 130 which may be a fiber optic, articulated arm, or an electrical cable etc At the distal end of delivery device 112 is a energy directing means 131 for directing the pulsed energy toward the surface tissue 116 and overlaymg tissue 118 overlaying the target tissue or structure 120 A nozzle 134 is useful for directing coolant from reservoir 135 to the tissue 118, and a valve 136 for controlling the coolant mterval A temperature sensor 137 may be used to momtor the temperature πse of the target tissue 118 Control system 106 monitors the temperature signal from sensor 137 and controls valve 136 and energy source 102 Reservoir 135 may be m the delivery device 112 or elsewhere, and contains a refrigerant which may be applied to surface tissue 120 by spraying said refrigerant from coolmg nozzle 124 in conjunction with delivery of pulsed treatment energy to the patient FIG 3 is a representative sample data plot of the temperature of surface tissue 116 and target tissue 120 achieved by methods and systems of the pπor art having precoolmg The waveforms are representative of oscilloscope-type traces which reproduce signals generated bv one or more thermal detectors In general, with piecooling the coolant is applied just pπor to the delivery to the pulsed energy Waveform 240 indicates the peπods of time and associated temperatures of the target tissue and the surface tissue duπng the processes of the pπor art
Initially, as indicated by time peπod 241, the temperature of the surface tissue 116 as well as the target tissue 120, as shown in FIGS 1 and 2. are at Ts and T, respectively It will be understood that typically the skin surface is at a temperature somewhat below actual body temperature Typically, this range might be between about 28 and about 34 degrees Celsius Furthermore, a target vem. hair follicle or other structure can be assumed to be at about or somewhat just below 37 degrees Celsius, or actual body temperature Once the refrigerant is applied to surface tissue 116 by opening valve 136 duπng a subsequent time peπod 244, the temperature Ts drops to a level determined by the length of time 244 for which the surface tissue 120 is exposed to the coolant. By way of example, for time peπods of about 30 milliseconds. Ts may drop from a typical temperature of about 32 degrees Celsius to just above 0 degrees Celsius However, as the target tissues 120 is deeper than the surface 116, initially T, is not significantly affected and may drop by only a few degrees A short delay 245 following delivery of refrigerant may be used, and is typically between 0 and 100 milliseconds This allows tune for coolmg of at least a layer of epidermis to a depth of 50 to 250 micrometers Following time peπods 244 and optional peπod 245, the pulsed energy is applied over predetermmed or other time peπod 246 The time peπod 246 depends on the size of the target and the fluence delivered, as indicated by principles of selective photothermalysis For example, m experiments with an Nd YAG laser operatmg at 1064 nanometers, one application of a 10 millisecond peπod and a fluence of 50 joules per square centimeter was sufficient to treat small blood vessels, and fluences of up to 150 joules per square centimeter and tune peπods of up to 200 milliseconds are useful for treatmg larger vessels of 1 to 3 millimeters in cross-section Duπng peπod 246 T, increases to a therapeutically effective value, whereas Ts remains below the threshold indicated as 250 for patient discomfort or tissue damage
Subsequent to treatment, the target tissue 116 cools by conduction of thermal energy to adjacent overlaying tissue 118 including the surface tissue 116. with a resultant temperature πse m the target tissue 120 dependant on the size and depth of the target tissue 120 As T, equalizes with suπoundmg tissue, the Ts may πse above the level of patient discomfort and even cause damage to surface tissue 116
FIG 3 is a representative sample data plot of the temperature of surface tissue 116 and target tissue 120 achieved by methods and systems of the pπor art having precoolmg
FIG 4 is a representative sample data plot of the temperature of surface tissue 116 and target tissue 120 achieved by a prefeπed embodiment of the method and system of the present mvention such as shown m FIGS 1 and 2 having precoolmg The method of the present mvention mcludes the process of precoolmg surface tissue 116 and target tissue 120 slightly, followed by a short tune peπod 245 and subsequent delivery of thermal energy to the body duπng time peπod 246 such as shown m FIG 3 In the present mvention, however, refrigerant is also applied subsequent to the energy pulse by opening valve 136 as desired or as indicated, thus keepmg Ts below the threshold for damage temperature 250 FIG 4 shows a pulse of coolant applied duπng tune peπod 248 which is subsequent to the application of pulsed energy duπng peπod 246 This results m thermal quenching of the surface tissue 116 The thermal quenching pulse or other flow of refrigerant or other means for coolmg is applied after the beginning of treatment peπod 246 and may be mitiated before or after the end of time peπod 246 It is unportant that the peak or highest temperature of the surface tissue 116 never πse above the threshold for damage temperature 250 The tune pomt at which the peak temperature in the surface tissue 116 is achieved is dependant on the size and depth of the target 120
In one experimental example, crvogemc fluid was applied to the surface tissue 116 within 10 milliseconds of the end of the energy pulse of tune peπod 246 and for a duration 248 of 20 milliseconds. For vascular treatment with an Nd:YAG laser with pulse widths of 5 milliseconds to 200 milliseconds, the peπod of thermal quenching 248 preferably 10 milliseconds to 30 milliseconds immediately after the treatment energy This sequence significantly reduced patient discomfort compared to treatment with out thermal quenchmg The effect of thermal quenchmg is not dependant on pre-coolmg and may be used as the only method of coolmg m many cases.
FIG. 5 is a representative sample data plot of the temperature of surface tissue and target tissue achieved by a prefeπed embodiment of the method and system of the present invention such as shown m FIGS. 1 and 2 without precooling. As in the method shown m FIG. 4. the thermal quenchmg pulse or other flow of refrigerant or other means for cooling over tune peπod 248 is applied after the beginning of treatment peπod 246 and may be initiated before or after the end of time peπod 246. It is important that the peak or highest temperature of the surface tissue 116 never πse above the threshold for damage temperature 250.
The present invention requires less cooling of the target tissue, structure or area duπng the treatment phase than is typically required, resultmg m more efficient heatmg of the selected target and less thermal damage to surrounding tissue.
It will be understood that while numerous preferred embodiments of the present mvention are presented herem, numerous of the individual elements and functional aspects of the embodiments are similar. Therefore, it will be understood that structural elements of the numerous apparatus disclosed herem havmg similar or identical function may have like reference numerals associated therewith.
In a preferred embodiment of the present invention, re-heating of tissue, especially target or subsurface tissue can be useful. U.S. Application Serial No. 09/185.490 filed Nov. 3, 1998 by Koop et al. teaches methods and systems for performing subsurface heatmg of mateπal and in incoφorated herem by reference in its entirety. In these methods, target or subsurface tissue is preheated to an elevated, non-destructive temperature which is somewhat below that of treatment. Thereafter, the temperature of the target tissue or structures is raised to treatment temperature Once this second mcrease in temperature is achieved, the target tissue or structures will conduct heat mto the body, especially to adjacent tissue and surface tissue, at which tune the post-coolmg of the present mvention can be mitiated so as to prevent damage to adjacent tissue or derrms or other surface tissue
Unless defined otherwise, all technical and scientific terms used herein have the same meanmg as commonly understood by one of ordmary skill m the art to which the present mvention belongs Although any methods and mateπals similar or equivalent to those descπbed can be used m the practice or testmg of the present mvention, the preferred methods and mateπals are now descπbed All publications and patent documents referenced m the present mvention are mcoφorated herem by reference
While the principles of the mvention have been made clear m illustrative embodiments, there will be immediately obvious to those skilled m the art many modifications of structure, arrangement, proportions, the elements, mateπals. and components used in the practice of the mvention, and otherwise, which are particularly adapted to specific environments and operative requirements without departing from those principles The appended claims are mtended to cover and embrace any and all such modifications, with the limits only of the true purview, spiπt and scope of the mvention ///

Claims

We claim: 1 A system for treatment of tissue with electromagnetic energy compπsmg. a pulsed electromagnetic energy source for treatment of targeted tissue; coolmg means for coolmg tissue adjacent to the targeted tissue. and control means for regulating the energy source and the coolmg means such that coolmg of tissue adjacent to the targeted tissue is svnchromzed to the delivery of the pulsed energy and prevents undesired temperature πse m surface tissue and m tissue adjacent to the targeted tissue.
2 The system of claim 1 wherem the pulsed energy source is a laser.
3. The system of claim 1 wherem the pulsed energy source is a flashlamp or filament lamp.
4 The system of claim 1 wherem the pulsed energy source is visible, infrared, or microwave electromagnetic energy
5 The system of claim 1 wherein the coolmg means provides a short spurt of refrigerant or other cryogenic fluid.
6 The system of claim 1 wherem the pulsed energy source has a pulse width between about 1 nanosecond and about 10 seconds.
7 The system of claim 1 wherem the control means provides cooling subsequent to delivery of the pulsed energy.
/// 8 The system of claun 7 wherem the coolmg means provides a pulse of refrigerant or other cryogenic fluid lastmg between 5 milliseconds and 1 second m duration beginning after the heatmg of target tissue from the pulsed energv source
9 The system of claun 7 wherem the coolmg means provides coolmg beginning after the heatmg of target tissue from the pulsed energy source
10 The system of claim 7 wherem the coolmg means provides coolmg beginning after the heatmg of target tissue to treatment temperature from the pulsed energy source
1 1 A method for treatment of target tissue or structures with a pulsed electromagnetic energy with thermal quenchmg of adjacent or surface tissue, the method compπsmg the following steps (A) Generatmg pulsed energy from an energy source, (B) Delivering the pulsed energy to the target tissue or structures with a delivery device, (C) Treating the target tissue or structures with the pulsed energy to cause selective thermally mediated treatment of the target tissue or structures, and (E) Thermal quenchmg of tissue adjacent or overlying the treated target tissue
12 The method of claim 11 m which the selective thermally mediated treatment of the target tissue or structures is for the treatment of vascular tissue
13 The method of claim 11 m which the selective thermally mediated treatment of the target tissue or structures is for the treatment of tissue containing collagen 14 The method of claun 11 in which the selective thermally mediated treatment of the target tissue or structures is for the treatment of cartilage
15 The method of claim 11 m which the selective thermallv mediated treatment of the target tissue or structures is for the treatment of tissue containing pigment
16 The method of claun 11 m which the selective thermally mediated treatment of the target tissue or structures is for the hair removal treatment
17 A method of thermal quenchmg of surface tissue duπng selective thermally mediated treatment of target tissue or structures, the method compπsmg the steps of delivering energy to the target tissue or structures to mcrease the temperature of the target tissue or structures to a predetermmed treatment temperature, and coolmg the surface tissue or other tissue adjacent the target tissue or structures to prevent undesired heatmg of the surface tissue or other tissue adjacent the target tissue
18 The method of claun 17 m which the step of coolmg is mitiated after elevation of the target tissue or structures to treatment temperature
19 The method of claun 17 m which the step of coolmg is mitiated pπor to elevation of the target tissue or structures to treatment temperature
/// 20 The method of claim 17 m which the step of coolmg is mitiated concurrently with elevation of the target tissue or structures to treatment temperature
21 The method of claun 17 m which the step of coolmg is mitiated subsequent to an mcrease m the temperature of the surface tissue or other tissue adjacent the target tissue or structures
22 The method of claim 17 m which the pulsed electromagnetic energy is delivered at a rate of between about 50 Joules per square centimeter and about 150 Joules per square centimeter
23 The method of claun 17 m which the pulsed electromagnetic energy has a pulse width of between about 5 milliseconds and about 200 milliseconds
24 The method of claun 17 m which the step of coolmg mcludes delivery of refπgerant to the surface tissue for a peπod of between about 10 milliseconds and about 30 milliseconds
25 The method of claim 17 m which the step of coolmg the surface tissue or other tissue adjacent the target tissue or structures is performed usmg passive coolmg means
26 The method of claim 17 m which the step of coolmg the surface tissue or other tissue adjacent the target tissue or structures is performed usmg dynamic coolmg means
/// 27 The method of claun 26 m which the dynamic coolmg means cools the surface tissue or other tissue adjacent the target tissue or structures by delivermg a liquid refrigerant to the surface tissue or other tissue adjacent the target tissue or structures
28 The method of claim 27 m which the liquid refrigerant is delivered to the surface tissue or other tissue adjacent the target tissue or structures for a peπod of time between about 10 milliseconds and about 30 milliseconds
29 The method of claim 17 in which the target tissue or structures is vems and m which the treatment is vascular treatment
30 The method of claun 17 m which the target tissue or structures is hair follicles and m which the treatment is hair removal
31 The method of claun 27 in which the target tissue or structures is tissue contammg pigmentation and in which the treatment is modification of the pigmentation
///
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US20030065313A1 (en) 2003-04-03
US6451007B1 (en) 2002-09-17
US20060282067A1 (en) 2006-12-14
WO2001008545A3 (en) 2008-02-28
AU6608900A (en) 2001-02-19
US20050154383A1 (en) 2005-07-14
US7637906B2 (en) 2009-12-29
DE10082526T1 (en) 2002-01-24
US7122029B2 (en) 2006-10-17

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