EP1274359A1 - Procede et appareil destines a un traitement thermique superficiel de la peau - Google Patents

Procede et appareil destines a un traitement thermique superficiel de la peau

Info

Publication number
EP1274359A1
EP1274359A1 EP00951775A EP00951775A EP1274359A1 EP 1274359 A1 EP1274359 A1 EP 1274359A1 EP 00951775 A EP00951775 A EP 00951775A EP 00951775 A EP00951775 A EP 00951775A EP 1274359 A1 EP1274359 A1 EP 1274359A1
Authority
EP
European Patent Office
Prior art keywords
arrangement
layer
heat
bulk substrate
absorbing layer
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP00951775A
Other languages
German (de)
English (en)
Inventor
Per-Arne Torstensson
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Gustafsson Morgan
Original Assignee
Gustafsson Morgan
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Gustafsson Morgan filed Critical Gustafsson Morgan
Publication of EP1274359A1 publication Critical patent/EP1274359A1/fr
Withdrawn legal-status Critical Current

Links

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
    • 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
    • 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
    • A61B18/22—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 the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B18/28—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 the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor for heating a thermal probe or absorber
    • 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
    • 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
    • A61B2018/0047—Upper parts of the skin, e.g. skin peeling or treatment of wrinkles
    • 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
    • A61B2018/1807—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 light other than laser radiation

Definitions

  • the present invention relates to an apparatus and method of superficial heat treatment of biological tissue preferably heat treatment and coagulation of the epidermal layers-stratum cornea, stratum lucidum and stratum granolosum.
  • Selective heat treatment of the epidermal layers is made for a number of reasons such as wrinkle removal, non-permanent hair removal, soft facial skin rejuvenation, enhancement of percutaneous drug administration and treatment of psoriasis, among others.
  • the prior art technology for coagulation, evaporation and ablation of the epidermal layers is based on direct interaction of coherent laser radiation with the tissue.
  • only a few types of laser sources are suitable for depth controlled tissue removal.
  • the problem is that the extinction depth of the laser wavelength in the epidermal layers must be in the range of a few ⁇ ms or less in the tissue to achieve a superficial absorption of the radiation.
  • the most commonly used lasers for superficial tissue removal are E ⁇ YAG and excimer laser at with emission wavelength of 2940 nm and 193 nm respectively.
  • the corresponding extinction depths are 3-5 im (in water) and 0.1 im (in protein).
  • the only laser type which can perform precise and predictable removal of epidermal layers is the excimer laser with emission wavelength of 193 nm.
  • Excimer lasers are very expensive and tedious to work with. Excimer lasers at 193 nm are also less suitable for beam delivery through standard fiber optical links due to quite high attenuation in waveguide based on fused silica (quartz) glass. The long term effects of exposing living cells to UV radiation is not fully investigated. There maybe an elevated risk of developing cancer associated with excimer laser treatment.
  • Laser sources in combination with contact probes with radiation absorbing layers are in principle possible to use for superficial tissue removal.
  • the use of a totally radiation absorbing layer covering a part of the surface of the probe will eliminate the problem with the extinction depth since all of the thermal energy will be transferred by conduction to the tissue.
  • the contact probes aimed for lasers normally have a very small effective area typically only a few square millimeters. There are several reasons for making these laser fed contact probes with such small surfaces areas.
  • One important aspect is that the pulse energy from lasers is limited due to the low electro optical efficiency of used lasers. Typically only a few percent of the energy required for laser pumping is converted to laser radiation energy. Therefore laser contact probes with radiation absorbing layers are less suitable for large area treatment.
  • the invention features a method of selective coagulation and shrinking of the epidermal layers, stratum cornea, stratum lucidum and stratum granolosum, without significantly damaging the underlaying tissue layers.
  • the method of the invention is based on skin surface contact heating probe with a radiation absorbing layer.
  • the absorbing layer is heated in a controlled manner by the concentrated radiation from a pulsed in-coherent arc lamp.
  • the radiation absorbing layer firmly attached to the distal surface of an bulk substrate that is brought in physical contact and gently pressed towards the skin in order to achieve a uniform contact surface.
  • the bulk substrate should be optically transparent over the complete emission spectrum of the radiation source.
  • the radiation absorbing layer is heated rapidly when illuminated by the concentrated incoherent radiation from a pulsed arc lamp.
  • the complete emission wavelength spectrum typically 0.2-2 im
  • the complete emission wavelength spectrum generated by an arc lamp will contribute to the heating of the absorptive layer.
  • coating material having an wavelength insensitive and high absorption coefficient matching the emission spectrum of the lamp the major part of the optical energy will be converted to heat in the absorptive layer.
  • the overall energy efficiency compared to lamp pump lasers is improved considerably.
  • Preferable choice of material for the absorbing layer having a high absorption coefficient in the range of a 0.2-3 im are carbon or a number oxides made from nickel, zirconium etc.
  • the thickness of the absorbing layer should be in the range 1-50 im preferably in the range 2-10 im. If the material composition of the abso ⁇ tive layer is not tissue compatible a protective overcoat layer of alumina oxide or silicon oxide would be necessary. The thickness of the protective layer by minimized typically 1-5 im.
  • contact fluids are water, saline solution, or ultrasonic contact gel.
  • the fluids may be based on silicone oils or also based on hyaluronic acids.
  • the most preferable choice is a gel mixture compound made of water, denatured alcohol, propylene glycol, glycerin, sodium hydroxide, PEG40 hydrogenated castor oil, panthenol and carbomer and Xylocaine.
  • the Xylocaine is a cutaneous anesthetic gel and will reduce pain during treatment.
  • the depth control of the heat effected (coagulated) tissue is made primarily by regulation of radiation pulse duration time and controlling the power density of the radiation on the absorbing layer.
  • the radiation power density is controlled by the regulation of the discharge current through the arc lamp.
  • the power level is adapted for the specific optical geometry and probe surface area. A smooth heating of the absorbing layer is guaranteed by mixing the light from the lamp in an optical waveguide having a length of at least ten times the diameter of probe cross section which typically is 10 mm.
  • the cross section of the wave guide is preferably round or rectangular having a cross sectional area of
  • a typical pulse duration time of the lamp is in the range 0.1-500 ms with a repetition rate of typically 0.5-5hz.
  • the heat effected depth of the epidermal layer would correspond to pulse length range of 0.1-500 ms will be 7-500 im according to Figure 2. Used definition of heat effected depth is the distance form the (heated) surface to a point inside the tissue where the increment of temperature is app. 10% of tissue surface temperature increment at the end of the heat pulse.
  • Equation (1) is valid for one dimensional heat flow which is true if the heat affected depth is much smaller than the cross section dimension of the surface heat source.
  • Eq (5) with eq (2) and (3) gives and estimation of required pulse energy per unit area for pulse length e:
  • the total energy required for heating both tissue and the bulk substrate on which the absorbing layer is attached gives the following equation : * (e*p*c) ,/2 *e' /2 [(e*p*c) t ' /2 +[(e*p*c) s Vl ] (7)
  • a preferred embodiment of a heat zinc is to attach the uncoated side of the bulk substrate (quartz) to a sufficiently large body of sapphire which has a high heat conductivity.
  • the sapphire body should continuously be cooled preferably using a peltier element in contact with the sapphire body.
  • the sapphire body is positioned in the beam path.
  • the sapphire body is the distal end of an optical waveguide i.e. the sapphire body is apart of the optical system.
  • the bulk substrate attachment to the sapphire body is made in an appropriate manner it could be made a disposal part.
  • the surface opposite to the absorbing layer can be prepared with a tin adhesive film so that the bulk substrate easily can be replaced when a new treatment starts.
  • a disposal probe bulk substrate prevents transfer of contagious infections among individuals.
  • the thickness of the bulk substrate which preferably is made of quartz should be in the range 10-1000 im.
  • the optimum thickness maybe calculated for a specific pulse repetition rate and pulse duration time.
  • Fig. 1 is represents a schematic of the device to be used in the practice of the invention.
  • reference numeral 1 designates a pulsed electromagnetic source such a laser concentrated by an appropriate optical system 2.
  • Reference numeral 3 represents a waveguide, while 4 is a disposable bulk substrate attached to the exit cross section of the waveguide.
  • Element 5 is a cooling device such as a Peltier unit.
  • Fig. 2 is a graph of the heat affected depth in the epidermis vs duration time of heat pulse.
  • Fig. 3 is a plot of the relative temperature profile versus relative depth inside the bulk body.
  • Fig. 4 is a graph of coagulation depth in epidermis versus duration time of energy pulse.
  • Fig. 5 is a schematic representation of how the device of figure 1 is used to treat the epidermis.
  • the numeral 1 designates a pulsed electromagnetic source preferably a gas discharge lamp or a laser.
  • the radiation emitted from the light source 1 is concentrated by use of an appropriate optical system 2.
  • the electromagnetic source comprises a discharge lamp
  • the light going in the backward direction is redirected towards the optical waveguide by the use of a back reflector system e.g. a parabolic or elliptical mirror.
  • a back reflector system e.g. a parabolic or elliptical mirror.
  • Other types back reflectors such as white diffuse ceramics can also be used if the dimensions of the light source is adapted to the size of the entrance geometry of the waveguide 3.
  • the concentrating optical system normally comprises a lens array system. All radiation going in the forward direction is then concentrated as much as possible into the entrance surface of the waveguide 3.
  • the typical cross section area of the waveguide entrance surface is 0.3-3 cm .
  • the waveguide 3 is preferably made of crystalline sapphire having a round or rectangular cross section. Other geometry's may also be used such as elliptical ones.
  • the choice of sapphire material in the waveguide is due to the high thermal conductivity of this material.
  • the appropriate length of the waveguide 3 is in the range is 20-60 mm.
  • a large cross section requires a longer waveguide since the main function of the waveguide besides pure radiation guidance is to smooth out the radiation field from the light source 1.
  • a disposable bulk substrate 4 is attached to the exit cross section of the waveguide with thin layer of radiation transparent optical glue 4.6 a combination of optical matching liquid together with means for mechanical fixation of the bulk substrate. The complete bulk substrate should be able to exchanged after medical treatment of an individual.
  • the dimensions of cross section geometry of the bulk substrate 4 should be made a little larger than the corresponding cross section dimensions of the waveguide 3 to avoid leakage of radiation.
  • the bulk substrate 4 comprises of a sheet of quarts glass 4.1 and a stacked layer of coatings comprising an radiation abso ⁇ tive layer 4.2, preferably a sputtered layer of carbon or oxide film having a thickness of 1-10 im and a non toxic and tissue compatible layer preferably made of polycrystalline sapphire having a thickness of 0.2-2 im.
  • a contact brining layer of paste or liquid should be applied on the epidermal layer 4.5 of the tissue 6 before treatment.
  • the contact bringing layer 4.4 comprising of paste or liquid shall have a boiling point of at least 100°C preferably 150 to 250°C.
  • Tissue anaesthetics could be included into the paste or liquid for pain control if necessary.
  • Excessive heat generated from the radiation abso ⁇ tion in the layer 4.2 should be removed by attachment of a cooling device to the proximal end of the waveguide 3.2.
  • the cooling device 5 could either be Peltier unit or metal body cooled by a circulating coolant.

Landscapes

  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Optics & Photonics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Electromagnetism (AREA)
  • Medical Informatics (AREA)
  • Otolaryngology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Laser Surgery Devices (AREA)
  • Radiation-Therapy Devices (AREA)
  • Thermotherapy And Cooling Therapy Devices (AREA)

Abstract

L'invention concerne un procédé et un appareil destinés au traitement thermique conductif, de profondeur réglable, de couches superficielles, de préférence, de tissus biologiques tels que les couches de l'épiderme. Le procédé de l'invention consiste à presser une couche mince absorbant les rayonnements, fixée à un substrat volumique, à faible diffusivité thermique directe (ou indirecte via une couche protectrice déposée sur la couche absorbante), en contact physique avec la surface de l'objet à traiter thermiquement. La section transversale de la couche d'absorption est le plus souvent de 1 cm2. Les couches absorbantes sont fermement fixées à un substrat volumique optiquement transparent dont le refroidissement est régulé de façon à évacuer un excès de chaleur de la couche absorbante et régulé en volume de façon à éliminer un excès de chaleur de la couche absorbante et du substrat volumique. Dans une réalisation préférée, la couche absorbante est chauffée par le rayonnement provenant d'une source électromagnétique cohérente à impulsions ou modulée, de préférence d'une lampe à arc à impulsions. La durée d'une impulsion habituelle est de 0,5-50 ms avec une fréquence de répétition de 0,5-5hz. La profondeur de la zone de tissu affectée par la chaleur est régulée précisément par optimisation de la durée de l'impulsion de rayonnement électromagnétique et de la quantité d'énergie dans l'impulsion délivrées par la lampe flash ainsi que par le refroidissement avant impulsion via le guide d'ondes.
EP00951775A 2000-02-22 2000-02-22 Procede et appareil destines a un traitement thermique superficiel de la peau Withdrawn EP1274359A1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/IB2000/001036 WO2001062170A1 (fr) 2000-02-22 2000-02-22 Procede et appareil destines a un traitement thermique superficiel de la peau

Publications (1)

Publication Number Publication Date
EP1274359A1 true EP1274359A1 (fr) 2003-01-15

Family

ID=11003953

Family Applications (1)

Application Number Title Priority Date Filing Date
EP00951775A Withdrawn EP1274359A1 (fr) 2000-02-22 2000-02-22 Procede et appareil destines a un traitement thermique superficiel de la peau

Country Status (5)

Country Link
EP (1) EP1274359A1 (fr)
JP (1) JP2004504074A (fr)
CN (1) CN1460008A (fr)
AU (1) AU6462200A (fr)
WO (1) WO2001062170A1 (fr)

Families Citing this family (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2007514117A (ja) * 2003-10-09 2007-05-31 キロランダ・テクノロジーズ・リミテッド 光発熱式チップ
DE102006023186B4 (de) * 2006-05-17 2012-02-23 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Transdermales therapeutisches System
EP2269501A1 (fr) 2009-07-03 2011-01-05 Levi Emmerik A. Dewaegenaere Système de détection et de traitement des infections ou inflammations
EP2269527A1 (fr) 2009-07-03 2011-01-05 Levi Emmerik A. Dewaegenaere Système et procédé de contrôle du fonctionnement d'une plaquette thérapeutique
EP2269544A1 (fr) * 2009-07-03 2011-01-05 Levi Emmerik A. Dewaegenaere Système de traitement thermique et appareil avec protocole commandé par rétroaction biologique
US8262302B1 (en) * 2011-12-20 2012-09-11 Elc Management Llc Kit for a heating applicator and product
CN105303043B (zh) * 2015-10-26 2018-04-03 中国科学院上海硅酸盐研究所 减少激光闪光法有限脉冲时间效应的数据处理方法
CN110394831A (zh) * 2019-08-14 2019-11-01 浙江美森电器有限公司 一种电弧去毛装置

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5968038A (en) * 1996-10-31 1999-10-19 University Of South Florida Laser powered heating elements
NL1004851C2 (nl) * 1996-12-20 1998-06-23 Gijsbe Gerardus Henricus Maria Inrichting en werkwijze voor het ablateren van organisch weefsel door middel van warmtepulsen opgewekt door korte elektromagnetische stralingspulsen.
US5830208A (en) * 1997-01-31 1998-11-03 Laserlite, Llc Peltier cooled apparatus and methods for dermatological treatment
EP1042033A1 (fr) * 1997-12-23 2000-10-11 ESC Medical Systems Ltd. Appareil pour traitement electromagnetique therapeutique
US6165170A (en) * 1998-01-29 2000-12-26 International Business Machines Corporation Laser dermablator and dermablation
US6569157B1 (en) * 1998-05-18 2003-05-27 Abbott Laboratories Removal of stratum corneum by means of light

Non-Patent Citations (1)

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Title
See references of WO0162170A1 *

Also Published As

Publication number Publication date
JP2004504074A (ja) 2004-02-12
AU6462200A (en) 2001-09-03
CN1460008A (zh) 2003-12-03
WO2001062170A1 (fr) 2001-08-30

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