Connect public, paid and private patent data with Google Patents Public Datasets

Apparatus for tissue treatment

Download PDF

Info

Publication number
USRE38670E1
USRE38670E1 US09973464 US97346401A USRE38670E US RE38670 E1 USRE38670 E1 US RE38670E1 US 09973464 US09973464 US 09973464 US 97346401 A US97346401 A US 97346401A US RE38670 E USRE38670 E US RE38670E
Authority
US
Grant status
Grant
Patent type
Prior art keywords
light
beam
tissue
handpiece
area
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.)
Expired - Lifetime
Application number
US09973464
Inventor
Bjarne Asah
Olav Balle-Petersen
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.)
MEDART AS
Original Assignee
Asah Medico AS
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
Grant date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/06Radiation therapy using light
    • A61N5/0613Apparatus adapted for a specific treatment
    • A61N5/0616Skin treatment other than tanning
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20Surgical 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
    • A61B18/203Surgical 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
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20Surgical 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
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017Electrical control of surgical instruments
    • A61B2017/00022Sensing or detecting at the treatment site
    • A61B2017/00057Light
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00743Type of operation; Specification of treatment sites
    • A61B2017/00747Dermatology
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00452Skin
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00452Skin
    • A61B2018/00458Deeper parts of the skin, e.g. treatment of vascular disorders or port wine stains
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00452Skin
    • A61B2018/0047Upper parts of the skin, e.g. skin peeling or treatment of wrinkles
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00452Skin
    • A61B2018/00476Hair follicles
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636Sensing and controlling the application of energy
    • A61B2018/00904Automatic detection of target tissue
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20Surgical 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
    • A61B2018/2015Miscellaneous features
    • A61B2018/2025Miscellaneous features with a pilot laser
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20Surgical 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
    • A61B2018/2035Beam shaping or redirecting; Optical components therefor
    • A61B2018/20351Scanning mechanisms
    • A61B2018/20359Scanning mechanisms by movable mirrors, e.g. galvanometric
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37Surgical systems with images on a monitor during operation
    • A61B2090/373Surgical systems with images on a monitor during operation using light, e.g. by using optical scanners
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/06Radiation therapy using light
    • A61N2005/0635Radiation therapy using light characterised by the body area to be irradiated
    • A61N2005/0643Applicators, probes irradiating specific body areas in close proximity
    • A61N2005/0644Handheld applicators
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/06Radiation therapy using light
    • A61N5/0613Apparatus adapted for a specific treatment
    • A61N5/0616Skin treatment other than tanning
    • A61N5/0617Hair treatment

Abstract

An apparatus for tissue treatment is provided, comprising a light emitter for emission of a first light beam, director for directing the first light beam towards a target area to be treated, detector for detecting at least one tissue parameter at the target area, and first light beam controller for controlling at least one parameter without interruption of the propagating light beam. The tissue parameter may be selected from the group of texture, elasticity, size and shape. The apparatus may be used for ablating a thin epidermal layer of the derma of a patient and also marks on the tissue such as marks from chloasma, liver spots, red spots, tattoos, blood vessels just below the surface, etc. as well as warts, wounds, hair follicles, etc. may be ablated or treated.

Description

FIELD OF THE INVENTION

The present invention relates to an apparatus with a handpiece for tissue treatment, such as cosmetic tissue resurfacing.

BACKGROUND OF THE INVENTION

It is known to utilise laser light for tissue treatment, such as cosmetic tissue resurfacing, removal of hair, photocoagulation of veins, etc.

During cosmetic tissue resurfacing, a laser ablates a thin epidermal layer of illuminated derma of a patient. During healing, a new epidermal layer is formed on the ablated surface having the look of the derma of a young person, i.e. the new epidermal layer is formed without previously existing scars, wrinkles, etc.

Lasers that operate at a wavelength that is absorbed in water are used for cosmetic tissue resurfacing. When the laser power density (W/mm2) at illuminated cells is sufficient, cellular water is superheated causing small explosions that disrupt heated cells.

During removal of an epidermal layer, it is essential not to damage underlying or surrounding tissue. Residual heat may cause non-ablated cells to char and become necrotic, whereby new scars may be formed and thus, it is desirable to apply laser power for a short time, to minimize transmission of conducted heat to underlying and surrounding tissue.

It is therefore desired to accurately control the amount of light energy transferred to derma to be ablated. The amount of energy must be sufficient for the dermal cells to vaporize and, simultaneously, the amount of residual energy heating non-ablated cells must be so low that non-ablated cells will not be damaged.

Apparatuses for cosmetic tissue resurfacing are known, comprising a CO2 laser emitting a laser beam and a laser articulating arm with mirrors for reflection of the laser beam, so that the laser beam is transmitted inside the articulating arm. Further, the arm has a number of joints, so that the arm can be moved around by an operator. A handpiece to be held by the operator is connected to the arm. The laser beam is moved or scanned across a target surface by movable mirrors connected to motors and mounted in the arm. The scan pattern of the laser beam is an archimedes spiral. The laser spot formed by the laser beam on the target surface moves along the spiral at a constant angular speed.

It is a disadvantage of the known apparatus that the energy density delivered to the target surface is non-uniform across the scanned surface area of the spiral, as more energy is delivered at the centre of the spiral than at the circumferential of the spiral.

It is another disadvantage of the known apparatus that the circular outline of the scan pattern leads to non-uniform scanning of an area that is larger than the area of the scan spiral as either 1) areas that have not been scanned will remain on the surface, when abutting spirals or 2) ablated areas will be scanned more than once, due to overlap of spirals.

It is yet another disadvantage of the known apparatus that evaporated derma is exhausted through the internal of the laser articulation arm, whereby optics and other members in the arm get dirty.

It is still another disadvantage of the known apparatus that it is very laborious to disassemble members, that may have been in contact with a patient, from the handpiece, e.g., for autoclaving.

It is still another disadvantage of the known apparatus that movement of the handpiece is restrained by the laser articulation arm, as the construction of tubes interconnected by joints is not fully flexible.

In addition, the apparatus typically has a large mass and a large inertia (typically also due to counter-balancing masses) which makes the operation and movement of the arm elaborate and heavy.

Under the name Uni-laser 450P, Asah Medico A/S, Denmark, markets an apparatus for cosmetic tissue resurfacing, comprising a CO2 laser and an optical fiber coupled to the laser at one end and to a handpiece at the other end. The laser beam is manually scanned across the treatment surface by corresponding movement of the handpiece whereby the quality of the treatment is determined and limited by the skill of the operator.

Apart from being able to accurately control the amount of light energy transmitted towards tissue to be treated, it is also desirable to be able to automatically control whether or not light is transmitted towards tissue. If, for example, a laser is pointed at healthy tissue, it is desirable that it is detected that the tissue is healthy and that transmission of a laser beam be inhibited whereby damage to healthy tissue is prevented.

It is a disadvantage of known apparatuses that the exact circumference of the surface tissue area to be treated is defined manually by the operator. Manual control easily results in accidental damage to healthy tissue due to involuntary movements of the hand.

In U.S. Pat. No. 5,531,740, an apparatus is disclosed for automatically delivering a laser beam to an intricated colored region of a treatment area, e.g. for laser photocoagulation treatment of malformed veins. Typically, venular malformation forms an extremely intricate pattern and consequently, the task of precisely delivering the laser beam exclusively to the malformed veins becomes quite formidable. During scanning over the treatment region, the color of tissue to be treated is detected and the laser automatically treats only areas having a specified color.

It is a disadvantage of the apparatus that it is bulky and cannot easily be moved into treatment positions in relation to various surfaces of a human body. Rather, a tissue surface to be treated has to be brought into a specific position in relation to the apparatus before treatment can take place.

It is still another disadvantage of the known apparatuses that the distance between the surface to be treated and the output laser beam optics is unknown so that the degree of focusing of the laser beam on the surface to be treated is dependent on the operator.

It is yet another disadvantage of known apparatuses that no feed-back on the quality of the treatment currently in progress is provided.

SUMMARY OF THE INVENTION

It is an object of the present invention to provide an apparatus for tissue treatment having a handpiece that can be moved around, i.e. traversed and rotated, freely by an operator, i.e. without exerting forces acting against the movement.

It is another object of the present invention to provide an apparatus for tissue treatment in which tissue type of tissue at the area to be illuminated by the treating light beam is detected and in which parameters of the laser beam is adjusted according to detected tissue type.

It is a further object of the present invention to provide an apparatus for tissue treatment that includes means for detecting the distance between the surface of tissue to be treated and the output optics focusing treating light onto the surface so that optimum focusing conditions may automatically be obtained during treatment.

It is still another object of the present invention to provide an apparatus for tissue treatment that includes a temperature measuring device for measurement of tissue surface temperature.

It is yet still another object of the present invention to provide an apparatus for tissue treatment that is adapted to automatically and accurately treat tissue to a desired depth with causing only a minimum of damage to surrounding tissue that are not treated.

It is a further object of the present invention to provide an apparatus for cosmetic tissue resurfacing that is adapted to ablate dermal cells uniformly and from a large area of a patient.

According to the invention, the above-mentioned and other objects are fulfilled by an apparatus for tissue treatment, comprising a light emitter for emission of a light beam and an optical fiber for transmission of the light beam. The fiber has a beam-inlet end that is aligned with the emitted light beam so that the light beam is coupled into the optical fiber and a beam-outlet end for emission of the transmitted light beam. Further, the apparatus comprises a handpiece coupled to the optical fiber at the beam-outlet end and comprising an output for emission of the first light beam towards a target area of tissue to be treated, detector means for detecting the type of tissue at the target area, and first light beam control means for controlling parameters of the first light beam emitted towards the target area in response to the detected type of tissue whereby various types of tissue can automatically be treated differently.

Cellular water absorbs light energy and transfers the light energy into heat. Applying light energy to the cells is therefore an efficient way of destroying, e.g. ablating, tissue. That, it is preferred to use light sources, such as lasers, generating light at wavelengths with a high absorption in water, preferably wavelengths larger than 190 nm, such as wavelengths in the range from 190 nm to 1900 nm, preferably from 700 nm to 900 nm, and even more preferred approximately 810 nm, or, preferably wavelengths larger than 1900 nm, such as wavelengths in the range from 1900 nm to 3000 nm, preferably from 1900 nm to 2100 nm, and even more preferred approximately 1940 nm, or, from 2800 nm to 3000 nm, and even more preferred approximately 2930 nm, or wavelengths equal to or greater than 4500 mm, such as wavelengths in the range from 4500 nm to 11000 nm, preferably from 4500 nm to 5500 nm, alternatively from 10000 nm to 11000 nm, such as around 10600 nm.

The apparatus according to the invention may be used for ablating a thin epidermal layer of the derma of a patient, removing marks on the tissue, such as marks from chloasma, liver spots, red spots, tattoos, blood wessels just below the surface, etc, as well as warts, wounds, hair follicles, etc, and hereafter the terms tissue and resurfacing will include these marks and treatments thereof.

It is preferred, that the light source utilized in the present invention is a laser, but other light sources, such as light emitting diodes and halogen bulbs, may be utilized.

The laser may be any laser capable of emitting light with sufficient power for illuminated cells to vaporize, such as CO2 lasers, YAG lasers, such as Erbium YAG lasers, Holmium YAG lasers, etc., semi conductor lasers, pulsed lasers, gas lasers, solid state lasers, Hg lasers, excimer lasers, etc.

Typically, a power density greater than about 50 W/mm2, such as a power density in the range from about 50 W/mm2 to about 180 W/mm2, is adequate for vaporizing cells with a minimum of damage to the surrounding tissue.

However, when removing hairs, the wavelength of the light is preferred to be approx. 800 nm. At this wavelength the absorbtion of the light in the hair follicles is lower than at higher wavelengths, and the power density must therefore be higher than 180 W/mm2, preferable higher than 300 W/mm2. Generally, the power density is adapted to the wavelength and the tissue to be treated.

The optical fiber may be any fiber, such as a polycrystalline silver halide fiber, etc, that is suitable for transmission of light emitted from the light emitter and that is made of a material that allows repeated bending of the fiber, so that an operator can freely manipulate the handpiece in order to direct the light beam toward various areas of a patient.

A handpiece is a single unit for conveniently holding in one hand by an operator of the handpiece.

It is preferred to shape the handpiece ergonomically so that a comfortable hand grip is provided for the operator of the apparatus. For example, it is preferred to direct the light beam towards a target area at a substantially right angle to the area. The ergonomic form of the handpiece allows the operator to point the light beam at a substantially right angle to the target surface without having to bend the wrist in an uncomfortable way.

As already mentioned, it is desirable to automatically control whether or not tissue towards which the hand piece is directed (the hand piece is said to be directed towards a specific area if that area is illuminated when the light beam emitted by the handpiece is turned on) is treated and to what extent it may be treated. For example, if the handpiece is directed towards healthy tissue, turn on of the light beam should be inhibited.

Tissue may be classified into specific tissue types according to predetermined values of various parameters, such as color, temperature, texture, elasticity, size, shape, etc.

For example various marks may be detected by their color. Thus, the detector means may comprise light detectors for detection of intensity of light emitted from tissue at the target area, the target area being the area the handpiece is currently directed at.

The light detector is preferably a semiconductor light detector, such as a photodiode, etc.

Further, the handpiece may comprise two light sources emitting light of different wavelengths, preferably two light emitting diodes, one for emission of light in the wavelength range where the light is considered red and the other for emission of light in the wavelength range where the light is considered green. The light sources may alternatively emit light in the ultra violet or infrared wavelength range. Light from the light sources is transmitted towards the target area and is reflected by tissue at the target area. The reflected light is detected by the detector means and the intensity of reflected light in the two wavelength ranges in question characterizes the type of tissue that is illuminated.

The first light beam control means comprises outputs for controlling various parameters of light emitted by the light emitter, such as wavelength, output power, duty cycle, etc. Based on tissue type parameter values as measured by the detector means, the first light beam control means adjusts parameters of the emitted light correspondingly. For example, when two light sources are utilized for detection of tissue type as previously described, predetermined reflected light intensity value ranges for the two wavelength ranges may be stored in a memory of the first light beam control means. During treatment, measured values of reflected light intensity are compared with the stored predetermined ranges and when measured values are within the stored ranges treatment is enabled and otherwise it is disabled.

Further, the wavelength and/or the power of treating light emitted by the light emitter may be adjusted according to the measured values. For example, a plurality of predetermined ranges of reflected light intensity may be stored in the memory and during treatment the measured values may be compared to the stored ranges and the value of the wavelength and/or the power of treating light may be set according to relations between measured values and stored ranges. Alternatively, the first light beam control means may calculate and control the wavelength and/or the power of treating light as a predetermined function of measured values of reflected light.

The output power of the first light beam may be adjusted by adjustment of the continuous output power of the light emitter, by adjustment of the duty cycle of the light emitter, etc.

The handpiece may comprise an infrared detector, such as an infrared photodetector, for detection of intensity of infrared light emitted from tissue at the target surface, e.g. for determination of the temperature of the tissue. Like color, temperature may be utilized for characterization of tissue types. Further, tissue temperature may be utilized for monitoring of treatment progress and quality. The temperature of treated tissue increases during treatment and measurement of tissue temperature may be utilized for verification of the effect of the treatment. For example, when a specific tissue temperature is reached within a specific area, treatment of that tissue may be terminated, e.g. further treatment may be inhibited, as sufficient treatment has already been accomplished. Further, if a certain temperature has not been reached during treatment, output power of the light emitter may be increased to increase efficiency of the treatment.

To obtain an optimum result of treatment, it is important to keep the light beam focused at the target area during treatment.

The handpiece may comprise means for automatically controlling the distance from the handpiece of the focus point in such a way that the light beam is automatically focused at the target area during treatment.

Thus, the detector means may comprise a detector array and array optics for forming an image of the target area on the array. Further, the detector means may comprise image processing means for processing the output signals from the detector array. Preferably, the imaging means is adapted to calculate the size of a spot of light illuminated by the first light beam, or another light source of the apparatus, and imaged onto the detector array.

The handpiece may further comprise output optics for focusing the first light beam onto the surface of tissue to be treated and movably positioned at the output of the handpiece for adjustment of the distance between the handpiece and the focus point, and focus control means for adjusting the position of the output optics in repsonse to the value of the calculated spot size.

According to another embodiment of the invention, two crossing visible light beams are emitted from the handpiece, the cross point of the beams indicating the focus point of the first beam. The imaging means are adapted to detect the number of spots imaged onto the detector array, and the focus control means are adapted to adjust the position of the output optics in response to the number of spots and, preferably, the distance between them (if more than one).

The handpiece may comprise deflection means that includes any optical component or components suitable for deflecting light of the wavelength in question, such as mirrors, prisms, grids, diffractive optical elements, such as holograms, etc, etc.

The deflecting means are preferably movably mounted for displacement of the deflecting means as a function of time, so that the light beam emitted from the handpiece can be scanned across a surface along a desired curve, while the handpiece is kept in a fixed position. Preferably, the deflecting means are rotatably mounted, and the actual deflection of the light beam is determined by the current angular position of the deflecting means. It is preferred that the surface is scanned along a substantially straight line.

Various actuators may be utilized to control positions of the deflecting and focusing means, such as piezo electric crystals, the displacement of which is controlled by applying a specific electric voltage to their electrodes, electro motors generating linear or rotational displacements, galvanometers, magnetically activated or controlled actuators, pneumatic actuators, hydraulic actuators, etc.

The positions of the deflecting means may be controlled by controlling means adapted to control the deflection means to deflect the light beam to traverse a target surface along a desired curve.

According to a preferred embodiment of the invention, a handpiece is provided, having two mirrors that are rotatably mounted in the path of the light beam in the handpiece. The rotational axis of the mirrors may be substantially perpendicular to each other in order to obtain two dimensional deflection of the light beam.

Alternatively, the movable deflecting means may comprise one mirror that is rotatable around two axes that may be substantially perpendicular to each other.

The mirrors may be connected to electro motors for angular positioning of the mirrors, e.g. each mirror may be directly connected to a corresponding shaft of a motor, whereby each motor is used for angular positioning of the corresponding mirror.

In order to minimize the size of the handpiece, it is preferred to mount the motors with their respective shafts in a common plane. For example, one motor may be a linear motor, such as a linear step motor, generating linear displacements. The shaft of this motor may be connected to the mirror at a first edge of the mirror, while a second and opposite edge of the mirror is rotatably connected to the handpiece. By pushing or pulling the first edge by the linear motor, the mirror is rotated about its rotational axis. The other motor, preferably a galvanometer, may be connected to the other mirror in the conventional way described above, whereby the two mirrors may be rotated around substantially perpendicular axes.

When a target area is scanned line by line, it is preferred that movement of one mirror generates the line scan, while movement of the other mirror moves the light beam to the next line. In the example above, the galvanometer preferably generates the line scan as the galvanometer can move the mirror at a high speed, and the linear motor preferably generates the displacement of the light beam to the next line to be scanned.

As mentioned earlier, it is preferred to control the amount of energy delivered to cells to be ablated, as the amount of energy must be sufficient for the dermal cells to vaporize and, simultaneously, the amount of residual energy heating non-ablated cells must be so low that non-ablated cells will not be seriously damaged. Thus, when an area of tissue is scanned, e.g. line by line, it is preferred that neighbouring lines substantially abut each other. Clinical investigations have shown that, typically, an overlap of 0.1 to 0.2 mm is acceptable, and a distance between scanned areas of up to 0.1-0.2 mm is acceptable.

In order to control positioning of curves on the target area this accurately, it is preferred to position the movable deflection means extremely accurately in the handpiece. In the preferred embodiment of the invention, this is accomplished by utilisation of printed circuit technology providing high accuracies of hole positioning of 0.05 mm. The mirrors are rotated around shafts that are mounted in printed circuit boards providing the required positioning accuracy. Further, the motors rotating the mirrors are also mounted on the printed circuit boards providing electrical connections to the motors and the mechanical support and positioning needed.

When scanning a scan area line by line, it is preferred to scan each line in the same direction ensuring uniform heating of cells across the scan area. Further, it is preferred to turn off the light beam, e.g. by switching off the light emitter, by inserting a light obstructing member in the light path of the beam, etc, while the light beam is moved from the end of a line having been scanned to the start of the next line to be scanned, to avoid over illuminating areas of the two lines to be scanned.

Instead of turning the light emitter off, the light beam may be moved at a speed significantly larger than the scan speed, during movement from the end of a line to the start of the next line.

Typically, the intensity within the beam of a light beam as generated by the light emitter varies as a normal function of the distance from the centre of the beam. The optical fiber may be designed or selected to be dispersive in such a way that the intensity function of the light beam emitted from the fiber as a function of the distance to the centre of the beam is substantially rectangular, i.e. the intensity of the beam leaving the fiber decays more slowly towards the edge of the beam than the intensity of a beam as generated by the light emitter whereby heat is more uniformly generated in cells across a scanned line of tissue.

By adequate control of the starting position of a line to be scanned and the stop position of scanning along the line, it is seen that scan areas of any shape may be generated. The shape of the scan area may for example be polygonal, such as rectangular, quadratic, triangular, etc., or circular, elliptic, etc.

The detector means may be utilized for detection of various tissue parameters during scanning of the first light beam across a tissue area so that treatment and tissue parameter determination are performed substantially simultaneously including adjustment of light beam parameters according to detected tissue parameter values.

However, it is presently preferred that the light beam control means further comprises switching means for preventing emission of the first light beam and being controlling by the first light beam control means so that emission of the first light beam is prevented during a first scan of the light beam from a predetermined first position to a predetermined second position along a predetermined path. The apparatus may further comprise tissue type storage means for storage of coherent data sets of signal values provided by the detector means at predetermined positions along the predetermined path of the light beam and the corresponding positions of the deflection means thereby mapping tissue parameters as a function of relative position within the target area of the tissue in the storage.

The first light beam control means may further be adapted to control parameters of the first light beam during a second movement of the light beam along the above-mentioned predetermined path in accordance with the coherent data sets stored.

For example, without automatic control of tissue treatment, removal of hair is a difficult task to perform as a large number of small spots having diameters of approximately 1 mm have to be pinpointed by the operator performing the treatment. According to the present invention, the surface tissue area with hair to be removed is scanned by the handpiece. Hereby the hair follicles are detected by color determinations as described above and their positions along the scanned path of the light beam are stored in the tissue type storage means. During a second and repeated scan of the tissue area, the treating light beam is turned on and off according to the content of the tissue type storage means so that solely the hair follicles detected during the first scan are treated preventing the surrounding tissue from being damaged.

Parameter values, such as color, temperature, etc, stored in the tissue type storage may be displayed on a display unit, such as a CRT, LCD, etc, e.g. as graphical three dimensional plots showing surface profiles of the actual parameters of scanned areas. Further, the parameter values may be processed, e.g. providing averages, weighted averages, correlation, cross-correlation, etc, and the value may be displayed, e.g. on the display unit or, on a separate display on the handpiece.

The output power of the first and treating light beam may be adjusted by adjusting the duty cycle of the beam, i.e. by pulse width modulating the light emitter. Thereby, a scanned line is broken into a plurality of line segments. A fade-in scan area may be created by starting the line with short pulses of light between longer periods of no light. As the line is traversed, the duration of light pulses is gradually increased and the periods with no light is gradually decreased. Finally, at the end of the fade-in area the light is not pulsed, and the scan line may be completed with maximum light intensity.

Similar, a fade-out scan area may be created by starting a scan line with maximum light intensity, and at the start of the fade-out area, the light emitter is pulse width modulated to transmit shorter and shorter pulses of light between longer and longer periods of no light. Finally, at the end of the fade-out area, the light is not pulsed, and the scan line is completed with no light intensity.

Fade-in or fade-out scan patterns may also be created by gradually increasing or decreasing, respectively, the output power of the light emitter, or by decreasing or increasing, respectively, the scan speed of the light beam, i.e. the speed at which the spot illuminated by the first light beam moves on a surface to be treated.

Alternatively, any combination of these methods may be used.

Various shapes, such as polygonal, such as rectangular, quadratic, triangular, etc, circular, elliptic, etc, of the area including fading area to be scanned by the first light beam may be selected by the user. Within the selected shape, treatment of tissue may be automatically controlled as described above, e.g. a rectangular shape of an area to be treated may be selected, however, if the handpiece is directed at healthy tissue the area will be scanned to determine tissue type and no treatment will be performed.

A scan line with fade-in and/or fade-out effects creates a smooth transition from a non-treated area of the tissue to a treated area of the tissue. This is advantageous when using the apparatus of the present invention for treatment of small marks on the tissue such as marks from chloasma, liver spots, red spots, tattos, blood wessels etc.

The first light beam control means may be adapted to control the intensity of the light beam and/or the velocity of the scanning light beam along a desired curve as a function of the position of the light beam inside the area of the target tissue area.

Within an area of tissue all of which is of a type to be ablated, the first light beam control means may be adapted to provide a substantially constant intensity of the light beam and a substantially constant scan velocity of the first light beam.

If desired, the fade-in and fade-out effect may be provided either by scanning the light beam with a velocity larger than the substantially constant scan velocity within the treatment area of tissue or, by decreasing the output power of the first light beam.

The first light beam control means may be adapted to control the power-per-area of the light beam when scanned along a desired curve on a target tissue area to be treated. For example, when ablating tissue it is presently preferred to maintain the power-per-area of the first light beam inside a first part of the target tissue area at a substantially constant level.

In order to create the fade-in or fade-out effect, the power-per-area of the light beam when outside a first part of the target tissue area may depend on the distance to the first part of the target tissue area, and it is preferred that the power-per-area of the light beam increases with decreasing distance to the first part of the target tissue area.

In the case where the first light beam is invisible, e.g. utilizing an infra red emitter, an ultra violet emitter, etc, a light source generating visible light may be provided for generating a visible light beam that is used to assist the operator by indicating areas towards which the invisible and treating light is directed during scanning. For example, the input connector of the handpiece may be further adapted to connect a second beam-outlet end of a second optical fiber for transmission of a visible light beam to the handpiece. The second optical fiber is preferably properly aligned in the connector in relation to the desired path of the visible light. The handpiece may further comprise second movable deflecting means for variable deflection of the visible light beam in such a way that the treating light beam and the visible light beams emitted from the output of the handpiece illuminate substantially the same area of a target surface.

Further, two crossing visible light beams may be emitted from the handpiece, the cross point of the beams indicating the focus point of the first beam.

Preferably, common moving deflecting means are utilised for deflection of all light beams emitted from the handpiece. Zinc selenite lenses may be utilized, as they are transparent for visible light as well as for infra-red light.

In order to further assist the operator of the apparatus, the visible light beam may, e.g. between scans of the treating light beam, be scanned around at least a part of the circumference of the scan area thereby indicating the size, shape and position of the scan area to be scanned.

When a polygonal shape of the scan area has been selected, the visible light beam may, e.g. between scans of the ablating light beam, be scanned along one edge of the polygon.

In order to further assist the operator of the apparatus, the temperature of the target tissue area may be measured immediately after treatment. The surface temperature is measured by measuring the infrared irradiation from the surface with the detector means of the handpiece. This temperature provide an objective measure of the quality of the treatment. A high temperature in the surface skin indicates that the energy has been absorbed in the surface tissue, whereas a low surface temperature indicates that the energy has been absorbed in the depths of the tissue. It is also possible to provide an interface to a PC (or any other calculating unit) for further calculations on the temperature data.

In order to assist the operator of the apparatus in keeping a constant distance from the output of the handpiece to the surface of the tissue to be ablated, the handpiece may comprise a distance member connected to the handpiece at the output with fastening means.

As the distance member will touch the patient, it is desirable to insert a new, disinfected member before treatment of a new patient and thus, it is preferred that the fastening means comprises a magnet so that a used distance member can easily be disconnected from the handpiece, e.g. for autoclaving, and so that a new member can easily be connected to the handpiece.

In order to increase the ease of use of the handpiece, it may be provided with interfacing means for selection of parameters of the cosmetic resurfacing apparatus. The interfacing means may comprise push buttons, selectors, rotary switches, etc. The interfacing means may also comprise a display for showing the mean temperature of the surface immediately after the treatment.

The parameters selectable from the handpiece may comprise the scan velocity, the ablating and the visible light beam intensities, the size and shape of the scan area, and fade-out effects.

Further scope of applicability of the present invention will become apparent from the detailed description given hereinafter. However, it should be understood that the detailed description and specific examples, while indicating preferred embodiments of the invention, are given by way of illustration only, since various changes and modifications within the spirit and scope of the invention will become apparent to those skilled in the art from this detailed description.

BRIEF DESCRIPTION OF THE DRAWINGS

In the following, a preferred embodiment of a tissue treatment apparatus comprising detector means will be described with reference to the drawings, wherein

FIG. 1 shows a cross section of a cable for transmission of light from a laser source to the handpiece according to the invention,

FIG. 2 shows a cross section of a handpiece according to the present invention,

FIG. 3 shows the lens system of the handpiece shown in FIG. 2 in treatment mode in greater detail,

FIG. 4 shows the dashed area of FIG. 2, the detector means in more detail,

FIG. 5 shows detector means of the handpiece shown in FIG. 2 in sensing mode in greater detail.

FIG. 6 shows a circular and a quadratic scan area,

FIG. 7 shows a circular and a quadratic scan area with a single-sided fade-out scan pattern,

FIG. 8 shows a circular and a quadratic scan area with a four-sided fade-out scan pattern, and

FIG. 9 shows a cross section of a standard laser beam and an example of a cross section of a laser beam more suitable for use in the handpiece of the present invention.

DETAILED DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a cross section of a cable 1 for transmission of light from a laser source to the handpiece of an apparatus for tissue treatment. An optical fiber 2 is positioned at the centre of the cable 1. The optical fiber 2 is made of silver chloride and silver bromide (silver halide), which is especially designed for light at a wavelength of app. 10.6 μm. The optical fiber 2 is covered by a cladding 3, also made of silver bromide and silver chloride but mixed in another ratio, which prevents the light travelling in the fiber 2 to escape from the fiber 2. The diameter of the fiber 2 is app. 500 μm, while the cladding 3 is app. 50 μm thick. The fiber 2 and the cladding 3 are protected against influence from the environment by a teflon tube 4. The fiber 2 and the cladding 3 are also protected against mechanical stress by a plastic tube 5 also protecting the teflon tube 4. The fiber 2, the cladding 3, the teflon tube 4 and the plastic tube 5 can be considered as an optical fiber unit 10. Included in the cable 1 are two glass fibers 6, 7 and a wire 8. The two glass fibers 6, 7 are specially designed optical fibres designed with a small NA (numerical aperture) designed for visible light at a wavelength of app. 650 nm. The wire 8 is provided for protecting the cable 1 against tensions and overloads. The optical fiber unit 10, the two glass fibers 6, 7, and the wire 8 are surrounded by a spiral tube 9 made of stainless steel. The optical fiber unit 10, the two glass fibers 6, 7, and the wire 8 are not fixed in position relative to each other inside the spiral tube 9, but can move in relative to each other inside the spiral tube 9, but can move in relation to each other. This makes the cable 1 very flexible when it is moved, and it provides at the same time a good protection of the fragile fibers 2, 6, 7. Inside the spiral tube 9 and along the optical fiber unit 10, the two glass fibers 6, 7, and the wire 8, compressed air is blown. The air is blown out in front of the optics, blowing away any ablated material that otherwise could deposit on the optics.

The light beam from a CO2 laser is coupled into the optical fiber 2 at one end of the fiber 2 positioned at one end of the cable 1. At the same end of the cable 1, light beams from two diode lasers are coupled into the glass fibers 6, 7, respectively. The light beams are transmitted in the respective fibers from the inlet end to the outlet end, which is connected to a handpiece.

FIG. 2 shows a handpiece 38 of an apparatus for tissue treatment according to the present invention. The cable 1 (not shown in FIG. 2) is connected to the handpiece 38 at a fiber inlet part 20, and guided through a tube 22 which is held in place in the handpiece 38 by the holding and heat distributing means 31. The fiber inlet part 20 also serves as a cable protecting sleeve. The light beams transmitted in the optical fiber 2 and the two glass fibers 6, 7 are radiated from the outlet ends of the fibers 2, 6, 7 through a lens system 39 (see FIG. 3) to an object, e.g. a human tissue surface. The outlet ends of the fibers 2, 6, 7 are positioned at a distance appropriate for the focusing lens 21 to focus the light from the fibers 2, 6, 7 on the object.

In FIG. 3, the lens system 39 is shown in greater detail. The light beams radiated from the outlet end of the fibers 2, 6, 7 are focused by the first focusing lens 21 and collimated by the collimating lens 23. The collimated light beam is transmitted from the collimating lens 23 via the deflecting means comprising a first mirror 24 and a second mirror 25 to a second focusing lens 30 which focuses the light beams on the target 40, which e.g. can be the facial tissue of a human being.

As shown in FIG. 2, the first mirror 24 is mounted on an indicator 45 of a galvanometer 26 positioned in the handpiece 38 of the tissue treatment apparatus according to the invention. When an electric current is sent through the coil of the galvanometer 26, the magnetic field generated by the current will make the indicator 45 rotate around the longitudinal axis of the indicator 45. The first mirror 24 will thereby by rotated, and the light beams will be deflected at an angle twice the angle rotated by the mirror 24.

The second mirror 25 is mounted on an arm 46 actuated by a linear actuator 29. When the linear actuator 29 activates the actuator arm 47, the arm 46, and thereby the second mirror 25, is rotated around the axle 48. A spring 28 is connected to one end of the arm 46 and to a non-moving part of the linear actuator 29 in the other end so as to neutralize wobble that may be present in the axle 48. When the second mirror 25 is rotated around the axle 48, the light incident on the second mirror 25 is deflected in an angle twice the angle rotated by the mirror 25. The linear actuator 29 may be controlled by applying a sequence of pulses across the terminals (not shown) of the actuator 29.

By controlling the current to the coil of the galvanometer 26 and the pulse sequence applied across the terminals of the linear actuator 29, the direction of light beams sent through the focusing lens 30 towards the target 40 can be controlled. It is thus possible to create different kinds of scan patterns of the light beam, such as rectangular or circular scan patterns.

A rotating arm 100 with a mirror 101 is by a solenoid 109 positioned in the beam path of the first laser light beam when the optical system is in a sensing mode as explained further below.

In FIG. 4, the part of the handpiece defined by the dashed line in FIG. 2 comprising the detector means is shown in greater detail. The detector means comprises a detector 110 and two light sources 102, 103 mounted in a holder for optical elements. The detector means further comprises a movable mirror 101. In sensing mode, the movable mirror 101 is positioned so as to transmit the sensing light beams emitted from the light sources 102, 103 mounted in the optical holder 107 via the fixed mirror 104 to the first mirror 24, the second mirror 25, and the second focusing lens 30 which focuses the light beams on the target 40. Likewise, the reflected sensing beams reflected from the target 40 are directed back to the detector means via the focusing lens 30 and the movable mirrors 24, 25. From the mirror 101 at the rotating arm 100 the reflected sensing beams are directed to the fixed mirror 104, wherefrom they are directed towards the detector 110 for intensity detection.

In FIG. 5 the detector means are schematically shown in greater detail, where the fixed mirror 104, however, is omitted to facilitate understanding of the operation. The light sources 102, 103 are laser diodes which emit light at different wavelengths. The emitted sensing light beams are directed one at the time through collimating lenses 113 to collimate the beams and to beamsplitters 111 reflecting the sensing light beams towards the movable mirror 101 wherefrom the light is directed to the target 40 via mirror 24, mirror 25 and focusing lens 30. As the sensing light beams pass the same optical system as the light beams emitted from the outlet end of the fibers, they may be scanned across the target 40 and the position of the sensing beams will be known at any time. The beams reflected from the target 40 follow the same path back to the beamsplitters 111. The polarisation of the light beams is changed when the light is reflected from the target 40, and since the transmittance of the beamsplitters 111 are dependent on the polarisation of the incident light beam the reflected sensing light beams reflected from the target 40 are transmitted through the beamsplitters, without reflection. Before the beam reaches the detector 110, it passes a polarisation filter 114 and a blockout filter 115 to increase signal to noise ratio, and a third focusing lens 112 to focus the beam at the detector. To determine the type of tissue at the target 40 a red and a green light beam from respectively light sources 102, 103, respectively, are alternately directed towards the target 40. The reflection of the red and the green light beams, respectively, from the target 40 are directed to the detector by the deflection means and are detected at the detector 110. The differences in the reflected light from light sources 102, 103 are calculated and the type of tissue, i.e. the color of the tissue, to be treated is thereby determined. Depending upon the type of tissue parameters to be determined, it is of course envisaged that the sensing beams may be visible light beams of any color, or it may be ultra violet light beams, or it may be infrared light beams.

The optics and electronics of the handpiece 38 are protected by a plastic housing 36 provided in an ergonomical shape. An air tube 34 may be positioned on the handpiece 38 for providing suction of air from in front of the optics of the handpiece 38 in order to absorb any material ablated from the tissue of the object being treated with the apparatus of the present invention.

The light beams from the two glass fibers 6, 7 transmitted from the cable 1 through the optics of the handpiece and to the object, intersects at a distance equal to the focal length of the focusing lens 30, i.e. at the distance where the light from the CO2 laser is focused. This is the distance at which the handpiece should be held from the object to get the best treatment result, and the intersection of the two visible light beams helps the operator keeping the correct distance to the tissue surface.

Because of the importance of keeping the CO2 focal point on the tissue surface, the presently preferred embodiment of the handpiece 38 further comprises a magnetic distance member 33 connected to the handpiece 38 with a magnet 32. As the distance member 33 is magnetic, it is easy to connect to and disconnect from the handpiece 38.

In the apparatus here shown the detector detects the light and calculates the type of tissue to be treated, but it is also possible to include an infrared light detector for determination of the temperature of the target.

Furthermore, in the apparatus shown a mirror 101 is mounted on the rotating arm 100, whereby simultaneously sensing and treatment is not possible. By replacing the mirror with a beamsplitter, it is possible to simultaneously treat and sense.

The present handpiece has three functions each with 3 different modes. In the first function, the operator may choose between high, medium, or low scan speed modes. When scanning on different types of tissue, it is preferred to adjust the scan speed of the light beam in stead of adjusting the output power of the light beam. When scanning on tissue with a low absorption of light, such as dry skin, it is preferred to generate a high power density on the tissue, and the scan speed mode should be set to low. When scanning on tissue with an average absorption of light, the scan speed mode should be set to medium, and when scanning on tissue with a high absorbtion of light, the high scan speed mode should be selected.

In the second function, the operator may chose between three different modes defining three different scan patterns, which patterns are a line, a circular pattern and a quadratic pattern.

The third function enables the operator to choose between three different sizes of the scan pattern. If the scan pattern is quadratic, the area may be approx. 9*9 mm, approx. 6*6 mm, or approx. 3*3 mm, if the scan pattern is circular, the diameter of the circle may be approx. 9 mm, approx. 6 mm, or approx. 3 mm, and if the scan pattern is a line, the length of the line may be approx. 9 mm, approx. 6 mm, or approx. 3 mm.

In FIG. 6, a quadratic scan area 52 and a circular scan area 51 are shown. The actual laser scan area is indicated by reference numeral 50, but only the scan areas 51, 52 are used for tissue treatment. The thin lines 53 and the thick lines 54 indicate the path which the laser beam follows during a scan. The thin lines 53 indicate parts of the scan where the laser is turned off, while the thick lines 54 indicate parts of the scan where the laser is turned on.

The scan is performed as a slow forward/fast return-scan (a TV-scan, but without interlacing). The scan starts at the lower left corner of the actual scan area 50. The laser beam is moved towards the right, and when the laser beam enters the tissue treatment scan area 51 or 52, the laser is turned on. When the laser beam leaves the tissue treatment scan area 51 or 52, the laser is turned off, and when the laser beam reaches the right edge of the actual scan area 59, the beam is quickly retraced or moved to the left edge of the actual scan area 50, and a new scan line can be initiated.

In stead of turning the laser on and off, the speed of the movement of the laser beam may be increased to a speed sufficiently high for the laser beam not to ablate the tissue surface.

The fast movement (trace and retrace) of the laser beam between the right and left edges of the actual scan area 50, is accomplished by controlling the galvanometer 26. In order to let the mirror 24 settle after the fast movement from the right edge of the actual scan area 50 to the left edge, the first part of the scan line is not used for tissue treatment. The slower movement of the laser beam from the bottom to the top of the actual scan area 50 is accomplished by controlling the linear actuator 29 in a constant movement of the mirror 25.

A quadratic scan area of approx. 9*9 mm comprises 30 scan lines, and the max. scanning speed is app. 300 mm/s.

The operator of the apparatus controls the scanning using a pedal. When the pedal is activated, a scanning starts. After finishing the scanning, the CO2 laser is turned off, and the visible light beam scans around at least a part of the circumference of the scan area 51 or 52 thereby indicating the size, shape and position of the scanned area 51 or 52. The operator may now move the handpiece and select a new scan area, e.g. a scan area abutting the area just scanned, and when the operator releases the pedal and again activates it, a new scanning will take place. In this way, the operator of the apparatus may easily scan larger areas of the tissue by scanning several neighbouring areas.

In FIG. 7, a quadratic scan area 52 and a circular scan area 51 with single-sided fade-out intensity scan lines 60 are shown. The fade-out intensity is accomplished by pulse modulating the laser power in shorter pulses as the intensity is faded out.

In FIG. 8, a quadratic scan area 52 and a circular scan area 51 with four-sided fade-out intensity scan lines 60 are shown.

The effect of using the fade-out intensity scan lines 60 is to create a smooth transition from a non-ablated area of the tissue to an ablated area.

The size and shape of the fade-in and fade-out scan areas may be selected using selectors on the handpiece 38.

It should be understood that a fade-in or a fade-out effect may be accomplished by gradually increasing or decreasing the intensity of the laser light, respectively, or by decreasing or increasing the speed of the movement of the laser beam, respectively.

In FIG. 9a, the beam profile for a standard laser beam transmitted via mirrors and standard lenses is shown. The beam profile is Gaussian with a high light intensity in the center of the beam. Only the high intensity center of the beam can ablate the tissue.

In FIG. 9b, a typical beam profile for a laser beam transmitted through the optical fiber 2 used in the apparatus according to the present invention is shown. The high intensity part of the beam profile is not limited to the center of the profile, but almost the complete beam profile has a sufficiently high intensity for ablating the tissue. When the laser light at 10.6 μm wavelength is transmitted through the 500 μm optical fiber 2, the laser light is changed from a single mode laser beam to a multi mode laser beam. A multi mode laser beam has a more uniform intensity profile compared to the single mode laser beam.

When using a Gaussian shaped beam, there is a risk of overexposing the tissue exposed by the center of the beam, while the parts of the tissue exposed by the edges of the beam are underexposed. This may result in thin lines of scars in the tissue. Using a non-gaussian shaped beam, as the beam provided by the optical fiber used in the apparatus according to the present invention, the risk of making scars in the tissue is minimized.

One of the advantages of using a broadened light beam is, that the risk of drawing lines on the tissue as with the high intensity Gaussian beam is minimized.

The invention being thus described, it will be obvious that the same may be varied in many ways. Such variations are not to be regarded as a departure from the spirit and scope of the invention, and all such modifications as would be obvious to one skilled in the art are intended to be included within the scope of the following claims.

Claims (34)

We claim:
1. A handpiece for an apparatus for tissue treatment, comprising:
an input adapted to receive a first beam-outlet end of a first optical fiber for alignment of the first optical fiber with an axis of the handpiece so that a first light beam emitted from the first beam-outlet end is transmitted substantially along the axis;
first movable deflection means for variable deflection of the first light beam emitted from the beam-outlet end;
an output for emission of the deflected first light beam towards a target area of tissue to be treated;
first deflection control means for controlling the first movable deflection means in such a way that the first light beam is deflected along a predetermined path across the target area to be treated;
detector means for detecting the type of tissue a the target area; and
first light beam control means for controlling parameters of the first light beam emitted towards the target area in response to the detected type of tissue whereby various types of tissue can automatically be treated differently.
2. The handpiece according to claim 1, wherein the detector means comprises light detectors for detection of intensity of light emitted from tissue at the target area.
3. The handpiece according to claim 1, wherein the detector means comprises infrared detectors for detection of temperature of tissue at the target area.
4. The handpiece according to claim 1, wherein the detector means comprises a detector array for detection of an image formed on the array.
5. The handpiece according to claim 4, further comprising image processing means for processing the image detected by the detector array.
6. The handpiece according to claim 5, wherein a size of a spot of light illuminated by the first light beam is calculatable by the imaging means.
7. The handpiece according to claim 6, further comprising:
output optics for focusing the first light beam onto the surface of tissue to be treated and movably positioned at the output of the handpiece; and
focus control means for adjusting the position of the output optics in response to the value of the calculated spot size.
8. The handpiece according to claim 1, wherein the first movable deflection means comprises a first mirror that is rotatable around a first axis.
9. The handpiece according to claim 8, wherein the first movable deflection means further comprises a second mirror that is rotatable around a second axis.
10. The handpiece according to claim 9, wherein the first axis is substantially perpendicular to the second axis.
11. The handpiece according to claim 10, wherein the first movable deflection means is controllable by the first deflection control means to deflect the first light beam to scan the target surface area line by line.
12. The handpiece according to claim 1, further comprising tissue type storage means for storage of coherent data sets of signal values provided by the detector means at predetermined positions along the predetermined path of the first light beam and the corresponding positions of the deflecting means thereby mapping tissue parameters as a function of relative positions along the path in the storage means.
13. The handpiece according to claim 12, wherein the first light beam control means is adapted to control parameters of the first light beam during a second scan of the light beam along the predetermined path in accordance with the coherent data sets stored in the tissue type storage means.
14. The handpiece according to claim 1, further comprising a first probing light source for illuminating tissue at the target area and wherein light that is reflected from the illuminated tissue is detectable by the detector means.
15. The handpiece according to claim 14, further comprising a second probing light source for illuminating tissue at the target area and wherein the first and second probing light sources emit light of different wavelengths.
16. The handpiece according to claim 15, wherein each of the first and second probing light sources comprises a light emitting diode.
17. The handpiece according to claim 16, wherein the first probing light source comprises a light emitting diode for emission of light in a red wavelength range.
18. The handpiece according to claim 16, wherein the second probing light source comprises a light emitting diode for emission of light in a green wavelength range.
19. The handpiece according to claim 14, wherein the type of tissue is characterized by intensity of the light that is reflected from the illuminated tissue.
20. The handpiece according to claim 1, further comprising user interface means for selection of parameters of the handpiece.
21. The handpiece according to claim 20, wherein the parameters comprise a scan velocity.
22. The handpiece according to claim 20, wherein the parameters comprise a first light beam intensity.
23. The handpiece according to claim 20, wherein the parameters comprise a size of the target surface area.
24. The handpiece according to claim 20, wherein the parameters comprise a shape of the target surface area.
25. The handpiece according to claim 1, wherein the input is further adapted to receive a second beam-outlet end of a second optical fiber for transmission of a visible second light beam to the handpiece and for alignment of the second optical fiber with the axis of the handpiece so that the visible second light beam emitted from the second beam-outlet end is transmitted substantially in parallel with the axis, and further comprising second movable deflection means for variable deflection of the visible second light beam in such a way that the first and the second light beams emitted from the output of the handpiece illuminate substantially the same area of a target surface.
26. The handpiece according to claim 25, wherein the first and the second movable deflection means are identical.
27. The handpiece according to claim 25, further comprising second deflection control means for controlling the second movable deflection means and for controlling the second movable deflection means in such a way that the visible second light beam is scanned around at least a part of a circumference of the target surface area thereby indicating the size, shape and position of the target surface area.
28. The handpiece according to claim 27, wherein the shape of the target surface area is polygonal and the second deflection control means is further adapted to control the second moving means in such a way that the visible second light beam is scanned along one edge of the polygon.
29. The handpiece according to claim 1, further comprising a distance member connected to the handpiece at the output with fastening means and for indicating the desired distance between a patient and the output.
30. The handpiece according to claim 29, wherein the fastening means comprises a magnet so that the distance member can readily be disconnected from the handpiece.
31. The handpiece according to claim 1, wherein the first light control means executes either a fade-in or fade-out scan pattern in response to the tissue type determined by the detector means.
32. The handpiece according to claim 31, wherein the fade-in and fade-out scan patterns are effected by varying the intensity of the first light beam.
33. The handpiece according to claim 1, wherein the deflection control means executes either a fade-in or fade-out scan pattern in response to the tissue type determined by the detector means.
34. The handpiece according to claim 33, wherein the fade-in and fade-out scan patterns are effected by varying the scan speed of the first light beam.
US09973464 1997-08-29 2001-10-11 Apparatus for tissue treatment Expired - Lifetime USRE38670E1 (en)

Priority Applications (5)

Application Number Priority Date Filing Date Title
DK0989/97 1997-08-29
DK98997 1997-08-29
US08974429 US6074382A (en) 1997-08-29 1997-11-19 Apparatus for tissue treatment
DKPA199900325 1999-03-08
US09973464 USRE38670E1 (en) 1997-08-29 2001-10-11 Apparatus for tissue treatment

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US09973464 USRE38670E1 (en) 1997-08-29 2001-10-11 Apparatus for tissue treatment

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US08974429 Reissue US6074382A (en) 1997-08-29 1997-11-19 Apparatus for tissue treatment

Publications (1)

Publication Number Publication Date
USRE38670E1 true USRE38670E1 (en) 2004-12-14

Family

ID=8092279

Family Applications (2)

Application Number Title Priority Date Filing Date
US09662373 Expired - Fee Related US6676654B1 (en) 1997-08-29 2000-09-13 Apparatus for tissue treatment and having a monitor for display of tissue features
US09973464 Expired - Lifetime USRE38670E1 (en) 1997-08-29 2001-10-11 Apparatus for tissue treatment

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US09662373 Expired - Fee Related US6676654B1 (en) 1997-08-29 2000-09-13 Apparatus for tissue treatment and having a monitor for display of tissue features

Country Status (2)

Country Link
US (2) US6676654B1 (en)
WO (1) WO2000053261A1 (en)

Cited By (42)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040143278A1 (en) * 2003-01-17 2004-07-22 Nova-Tech Engineering, Inc. Apparatus and method for upper and lower beak treatment
US20050154380A1 (en) * 2003-12-23 2005-07-14 Debenedictis Leonard C. Method and apparatus for monitoring and controlling laser-induced tissue treatment
US20050171517A1 (en) * 1996-12-02 2005-08-04 Palomar Medical Technologies, Inc. System for electromagnetic radiation dermatology and head for use therewith
US20050285928A1 (en) * 2003-12-31 2005-12-29 Broome Barry G Optical pattern generator using a single rotating component
US20060089687A1 (en) * 2002-12-12 2006-04-27 Greg Spooner System for controlled spatially-selective epidermal pigmentation phototherapy with UVA LEDs
US20060119920A1 (en) * 2003-12-31 2006-06-08 Debenedictis Leonard C High speed, high efficiency optical pattern generator using rotating optical elements
US20060217695A1 (en) * 2003-12-31 2006-09-28 Debenedictis Leonard C Optically-induced treatment of internal tissue
US20070060984A1 (en) * 2005-09-09 2007-03-15 Webb James S Apparatus and method for optical stimulation of nerves and other animal tissue
US20070106284A1 (en) * 2001-08-23 2007-05-10 Jerry Siegel Apparatus and method for performing radiation energy treatments
US20070239142A1 (en) * 2006-03-10 2007-10-11 Palomar Medical Technologies, Inc. Photocosmetic device
US20070244526A1 (en) * 2006-04-14 2007-10-18 Asa S.R.L. Laser apparatus for therapeutic applications
US20080058795A1 (en) * 2006-04-12 2008-03-06 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Systems for autofluorescent imaging and target ablation
US20080077198A1 (en) * 2006-09-21 2008-03-27 Aculight Corporation Miniature apparatus and method for optical stimulation of nerves and other animal tissue
US20080147053A1 (en) * 2006-12-15 2008-06-19 Korea Electro Technology Research Institute Apparatus and method for photodynamic diagnosis and therapy of skin diseases and light source system thereof
US7722656B1 (en) 2005-02-25 2010-05-25 Kim Robin Segal Device and method for stimulating hair growth
US7758621B2 (en) 1997-05-15 2010-07-20 Palomar Medical Technologies, Inc. Method and apparatus for therapeutic EMR treatment on the skin
US7763016B2 (en) 1997-05-15 2010-07-27 Palomar Medical Technologies, Inc. Light energy delivery head
US7883536B1 (en) 2007-01-19 2011-02-08 Lockheed Martin Corporation Hybrid optical-electrical probes
US20110087310A1 (en) * 2009-10-12 2011-04-14 Wellmike Enterprise Co., Ltd. Hair-growth caring apparatus
US7942915B2 (en) 2002-05-23 2011-05-17 Palomar Medical Technologies, Inc. Phototreatment device for use with coolants
US8012189B1 (en) 2007-01-11 2011-09-06 Lockheed Martin Corporation Method and vestibular implant using optical stimulation of nerves
US8160696B2 (en) 2008-10-03 2012-04-17 Lockheed Martin Corporation Nerve stimulator and method using simultaneous electrical and optical signals
US8182473B2 (en) 1999-01-08 2012-05-22 Palomar Medical Technologies Cooling system for a photocosmetic device
US8268332B2 (en) 2004-04-01 2012-09-18 The General Hospital Corporation Method for dermatological treatment using chromophores
US8346347B2 (en) 2005-09-15 2013-01-01 Palomar Medical Technologies, Inc. Skin optical characterization device
US8475506B1 (en) 2007-08-13 2013-07-02 Lockheed Martin Corporation VCSEL array stimulator apparatus and method for light stimulation of bodily tissues
US8498699B2 (en) 2008-10-03 2013-07-30 Lockheed Martin Company Method and nerve stimulator using simultaneous electrical and optical signals
US8652187B2 (en) 2010-05-28 2014-02-18 Lockheed Martin Corporation Cuff apparatus and method for optical and/or electrical nerve stimulation of peripheral nerves
US8709078B1 (en) 2011-08-03 2014-04-29 Lockheed Martin Corporation Ocular implant with substantially constant retinal spacing for transmission of nerve-stimulation light
US8744570B2 (en) 2009-01-23 2014-06-03 Lockheed Martin Corporation Optical stimulation of the brainstem and/or midbrain, including auditory areas
US8747447B2 (en) 2011-07-22 2014-06-10 Lockheed Martin Corporation Cochlear implant and method enabling enhanced music perception
US8915948B2 (en) 2002-06-19 2014-12-23 Palomar Medical Technologies, Llc Method and apparatus for photothermal treatment of tissue at depth
US8929973B1 (en) 2005-10-24 2015-01-06 Lockheed Martin Corporation Apparatus and method for characterizing optical sources used with human and animal tissues
US8945197B1 (en) 2005-10-24 2015-02-03 Lockheed Martin Corporation Sight-restoring visual prosthetic and method using infrared nerve-stimulation light
US8956396B1 (en) 2005-10-24 2015-02-17 Lockheed Martin Corporation Eye-tracking visual prosthetic and method
US8996131B1 (en) 2006-09-28 2015-03-31 Lockheed Martin Corporation Apparatus and method for managing chronic pain with infrared light sources and heat
US9011329B2 (en) 2004-04-19 2015-04-21 Searete Llc Lumenally-active device
US9028536B2 (en) 2006-08-02 2015-05-12 Cynosure, Inc. Picosecond laser apparatus and methods for its operation and use
US9173837B2 (en) 2004-04-19 2015-11-03 The Invention Science Fund I, Llc Controllable release nasal system
US9198563B2 (en) 2006-04-12 2015-12-01 The Invention Science Fund I, Llc Temporal control of a lumen traveling device in a body tube tree
US9780518B2 (en) 2012-04-18 2017-10-03 Cynosure, Inc. Picosecond laser apparatus and methods for treating target tissues with same
US9801527B2 (en) 2004-04-19 2017-10-31 Gearbox, Llc Lumen-traveling biological interface device

Families Citing this family (107)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060149343A1 (en) * 1996-12-02 2006-07-06 Palomar Medical Technologies, Inc. Cooling system for a photocosmetic device
US6104959A (en) 1997-07-31 2000-08-15 Microwave Medical Corp. Method and apparatus for treating subcutaneous histological features
EP1251791A1 (en) * 2000-01-25 2002-10-30 Palomar Medical Technologies, Inc. Method and apparatus for medical treatment utilizing long duration electromagnetic radiation
US6746444B2 (en) * 2000-12-18 2004-06-08 Douglas J. Key Method of amplifying a beneficial selective skin response to light energy
CA2433022C (en) * 2000-12-28 2016-12-06 Palomar Medical Technologies, Inc. Method and apparatus for therapeutic emr treatment of the skin
US20080183162A1 (en) * 2000-12-28 2008-07-31 Palomar Medical Technologies, Inc. Methods And Devices For Fractional Ablation Of Tissue
US20080132886A1 (en) * 2004-04-09 2008-06-05 Palomar Medical Technologies, Inc. Use of fractional emr technology on incisions and internal tissues
FR2818889A1 (en) * 2000-12-29 2002-07-05 Jean Louis Savoyet Laser hair removal device, uses micro-camera in laser beam delivery hand piece to provide image of skin region which is magnified and used to control power delivered by laser to reduce skin damage
EP1226787A3 (en) * 2001-01-29 2003-12-17 Laserwave S.r.l. Device for cutaneous treatments using optical radiation
US20060206103A1 (en) * 2001-03-02 2006-09-14 Palomar Medical Technologies, Inc. Dermatological treatment device
EP1365699A2 (en) * 2001-03-02 2003-12-03 Palomar Medical Technologies, Inc. Apparatus and method for photocosmetic and photodermatological treatment
US6887233B2 (en) * 2001-03-22 2005-05-03 Lumenis, Inc. Scanning laser handpiece with shaped output beam
WO2003017670A1 (en) * 2001-08-15 2003-02-27 Reliant Technologies, Inc. Method and apparatus for thermal ablation of biological tissue
US20040147984A1 (en) * 2001-11-29 2004-07-29 Palomar Medical Technologies, Inc. Methods and apparatus for delivering low power optical treatments
US20030216719A1 (en) * 2001-12-12 2003-11-20 Len Debenedictis Method and apparatus for treating skin using patterns of optical energy
US20030109860A1 (en) * 2001-12-12 2003-06-12 Michael Black Multiple laser treatment
US20030109787A1 (en) * 2001-12-12 2003-06-12 Michael Black Multiple laser diagnostics
US20040082940A1 (en) * 2002-10-22 2004-04-29 Michael Black Dermatological apparatus and method
WO2003057059A1 (en) * 2001-12-27 2003-07-17 Palomar Medical Technologies, Inc. Method and apparatus for improved vascular related treatment
US7263255B2 (en) * 2002-04-08 2007-08-28 Lumenis Inc. System, method and apparatus for providing uniform illumination
US7351252B2 (en) * 2002-06-19 2008-04-01 Palomar Medical Technologies, Inc. Method and apparatus for photothermal treatment of tissue at depth
US7201766B2 (en) * 2002-07-03 2007-04-10 Life Support Technologies, Inc. Methods and apparatus for light therapy
WO2004033040A1 (en) * 2002-10-07 2004-04-22 Palomar Medical Technologies, Inc. Apparatus for performing photobiostimulation
US20070213792A1 (en) * 2002-10-07 2007-09-13 Palomar Medical Technologies, Inc. Treatment Of Tissue Volume With Radiant Energy
JP2006511275A (en) * 2002-12-20 2006-04-06 パロマー・メディカル・テクノロジーズ・インコーポレイテッドPalomar Medical Technologies,Inc. Phototherapy device acne and other follicle disorders
CA2515843A1 (en) * 2003-02-19 2004-09-02 Palomar Medical Technologies, Inc. Method and apparatus for treating pseudofolliculitis barbae
DE202004021226U1 (en) 2003-03-27 2007-07-26 The General Hospital Corp., Boston Device for dermatological treatment and fractional resurfacing the skin
US8251057B2 (en) 2003-06-30 2012-08-28 Life Support Technologies, Inc. Hyperbaric chamber control and/or monitoring system and methods for using the same
JP2007531544A (en) * 2003-07-11 2007-11-08 リライアント・テクノロジーズ・インコーポレイテッドReliant Technologies, Inc. Method and apparatus for fractionation phototherapy of skin
US20050065577A1 (en) * 2003-09-23 2005-03-24 Mcarthur Frank G. Low level laser tissue treatment
US7309335B2 (en) * 2003-12-31 2007-12-18 Palomar Medical Technologies, Inc. Dermatological treatment with visualization
US7090670B2 (en) * 2003-12-31 2006-08-15 Reliant Technologies, Inc. Multi-spot laser surgical apparatus and method
GB0402321D0 (en) * 2004-02-03 2004-03-10 Cyden Ltd Hair removal
US20060020309A1 (en) * 2004-04-09 2006-01-26 Palomar Medical Technologies, Inc. Methods and products for producing lattices of EMR-treated islets in tissues, and uses therefor
EP1591076A3 (en) * 2004-04-28 2006-05-31 W & H Dentalwerk Bürmoss GmbH Dental laser treatment device
US7761945B2 (en) 2004-05-28 2010-07-27 Life Support Technologies, Inc. Apparatus and methods for preventing pressure ulcers in bedfast patients
US7413572B2 (en) 2004-06-14 2008-08-19 Reliant Technologies, Inc. Adaptive control of optical pulses for laser medicine
FR2872405B1 (en) * 2004-07-02 2006-11-10 Biomedical Electronics Method for configuration of a skin treatment device using light sources
DE102004050143A1 (en) * 2004-10-14 2006-04-27 EKA Gesellschaft für medizinisch-technische Geräte mbH Device for the treatment of visible fine surface veins
US20060253176A1 (en) * 2005-02-18 2006-11-09 Palomar Medical Technologies, Inc. Dermatological treatment device with deflector optic
DE102005010723A1 (en) * 2005-02-24 2006-08-31 LÜLLAU, Friedrich UV irradiation device for acting upon biological cellular structures, especially the skin, for medical and therapeutic purposes, has means for matching UV exposure geometries to those areas requiring treatment
EP1853190A4 (en) * 2005-03-02 2008-08-13 Meridian Co Ltd Adipose resolve apparatus for low-power laser
JP2009506835A (en) 2005-08-29 2009-02-19 リライアント・テクノロジーズ・インコーポレイテッドReliant Technologies, Inc. Method and apparatus for monitoring and controlling the thermally-induced tissue treatment
US20080058782A1 (en) * 2006-08-29 2008-03-06 Reliant Technologies, Inc. Method and apparatus for monitoring and controlling density of fractional tissue treatments
US8603084B2 (en) 2005-12-06 2013-12-10 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing the formation of a lesion in tissue
US8033284B2 (en) * 2006-01-11 2011-10-11 Curaelase, Inc. Therapeutic laser treatment
US20070194717A1 (en) * 2006-02-17 2007-08-23 Palomar Medical Technologies, Inc. Lamp for use in a tissue treatment device
US20070219604A1 (en) * 2006-03-20 2007-09-20 Palomar Medical Technologies, Inc. Treatment of tissue with radiant energy
US20070255355A1 (en) * 2006-04-06 2007-11-01 Palomar Medical Technologies, Inc. Apparatus and method for skin treatment with compression and decompression
US20070239145A1 (en) * 2006-04-11 2007-10-11 Raphael Laderman System and method to assist in the treatment of skin conditions
US20070260230A1 (en) * 2006-05-04 2007-11-08 Reliant Technologies, Inc. Opto-mechanical Apparatus and Method for Dermatological Treatment
GB2439286B (en) 2006-06-22 2010-09-15 Dezac Group Ltd Apparatus and methods for skin treatment
CN101478928B (en) * 2006-06-26 2013-04-24 皇家飞利浦电子股份有限公司 Device and method for the treatment of skin, and use of the device
US20080015553A1 (en) * 2006-07-12 2008-01-17 Jaime Zacharias Steering laser treatment system and method of use
US7862555B2 (en) 2006-07-13 2011-01-04 Reliant Technologies Apparatus and method for adjustable fractional optical dermatological treatment
US20100039385A1 (en) * 2006-08-03 2010-02-18 Schneider Paul P Computer Peripheral with Integrated Electromagnetic Radiation Therapy
US7612763B2 (en) * 2006-08-03 2009-11-03 Schneider Data Technologies Computer peripheral with integrated infrared therapy and method of making same
US20080033418A1 (en) * 2006-08-04 2008-02-07 Nields Morgan W Methods for monitoring thermal ablation
US8556888B2 (en) 2006-08-04 2013-10-15 INTIO, Inc. Methods and apparatuses for performing and monitoring thermal ablation
US20080033419A1 (en) * 2006-08-04 2008-02-07 Nields Morgan W Method for planning, performing and monitoring thermal ablation
US7871406B2 (en) 2006-08-04 2011-01-18 INTIO, Inc. Methods for planning and performing thermal ablation
US20080161745A1 (en) * 2006-09-08 2008-07-03 Oliver Stumpp Bleaching of contrast enhancing agent applied to skin for use with a dermatological treatment system
US20080091249A1 (en) * 2006-10-11 2008-04-17 Bwt Property, Inc. Photobiomodulation Apparatus with Enhanced Performance and Safety Features
US20080161782A1 (en) * 2006-10-26 2008-07-03 Reliant Technologies, Inc. Micropore delivery of active substances
EP1920798A1 (en) * 2006-11-08 2008-05-14 Roewer, Norbert, Univ.-Prof. Dr. med. Infrared irradiation device for irradiating human skin
US20080154247A1 (en) * 2006-12-20 2008-06-26 Reliant Technologies, Inc. Apparatus and method for hair removal and follicle devitalization
ES2333924B1 (en) * 2007-01-12 2010-12-03 Nita 54 S.L. Collection system setup parameters for laser depilation.
CN101711134B (en) 2007-04-19 2016-08-17 米勒玛尔实验室公司 System for applying microwave energy to the tissue and produce a tissue layer effect in a tissue system
JP5545668B2 (en) 2007-12-12 2014-07-09 ミラマー ラブズ, インコーポレイテッド System for non-invasive tissue treatment using microwave energy, equipment and procedure, and Procedures
EP2142129A4 (en) * 2007-04-19 2011-04-20 Miramar Labs Inc Methods and apparatus for reducing sweat production
US20100114086A1 (en) * 2007-04-19 2010-05-06 Deem Mark E Methods, devices, and systems for non-invasive delivery of microwave therapy
EP2271276A4 (en) * 2008-04-17 2013-01-23 Miramar Labs Inc Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy
KR101654863B1 (en) * 2007-12-12 2016-09-22 미라마 랩스 인코포레이티드 Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy
US20080262484A1 (en) * 2007-04-23 2008-10-23 Nlight Photonics Corporation Motion-controlled laser surface treatment apparatus
KR20100029235A (en) * 2007-06-08 2010-03-16 싸이노슈어, 인코포레이티드 Surgical waveguide
EP2025299A1 (en) * 2007-08-16 2009-02-18 Optical System & Research for Industry and Science Osyris Method and system for controlling a treatment by sub-cutaneous or intra-cutaneous irradiation using electromagnetic radiation
EP2030586B1 (en) * 2007-09-01 2011-05-11 Fotona d.d. Laser system for medical and cosmetic applications
WO2009052866A1 (en) * 2007-10-25 2009-04-30 Pantec Biosolutions Ag Laser device and method for ablating biological tissue
US20090149930A1 (en) * 2007-12-07 2009-06-11 Thermage, Inc. Apparatus and methods for cooling a treatment apparatus configured to non-invasively deliver electromagnetic energy to a patient's tissue
US20090177253A1 (en) * 2008-01-08 2009-07-09 Oregon Aesthetic Technologies Skin therapy system
JP5497664B2 (en) * 2008-01-14 2014-05-21 コーニンクレッカ フィリップス エヌ ヴェ Treatment system having a temperature control unit
US8155416B2 (en) 2008-02-04 2012-04-10 INTIO, Inc. Methods and apparatuses for planning, performing, monitoring and assessing thermal ablation
CN101977560B (en) * 2008-03-21 2013-06-12 皇家飞利浦电子股份有限公司 Hair removal system and method
US7671327B2 (en) 2008-04-22 2010-03-02 Candela Corporation Self calibrating irradiation system
US20100041998A1 (en) * 2008-08-18 2010-02-18 Postel Olivier B Method for Detecting and/or Monitoring a Wound Using Infrared Thermal Imaging
DE102008045824A1 (en) * 2008-09-05 2010-03-11 livetec Ingenieurbüro GmbH Treatment device for external treatment of human or animal body for simulating cells of nerves and muscles, has sensor directly or indirectly arranged at fastening device, and controlling device connected with sensor
EP2163218A1 (en) * 2008-09-16 2010-03-17 Osyris Medical Device for treating part of a human or animal body comprising an instrument for dispensing and/or an instrument for locally sucking up treatment doses and means for controlling dosimetry
DE102008048409A1 (en) * 2008-09-23 2010-03-25 Megasun Invest Ag Method and apparatus for hair removal
US20120046653A1 (en) * 2009-03-05 2012-02-23 Cynosure, Inc. Pulsed therapeutic light system and method
EP2238939B1 (en) * 2009-03-31 2012-03-28 Novavision Group S.r.l Control and support system for blemish treatment apparatus
US9414889B2 (en) * 2009-09-04 2016-08-16 Restoration Robotics, Inc. Follicular unit harvesting tool
US20110071601A1 (en) * 2009-09-23 2011-03-24 Resteche Llc Keyboard with integrated electromagnetic radiation therapy
WO2011044248A3 (en) * 2009-10-06 2011-08-18 Cardiofocus, Inc. Cardiac ablation image analysis system and process
WO2011085225A1 (en) * 2010-01-08 2011-07-14 Wake Forest University Health Sciences Delivery system
US20110172746A1 (en) * 2010-01-12 2011-07-14 Roger Porter High Level Laser Therapy Apparatus and Methods
DE102010009554A1 (en) 2010-02-26 2011-09-01 Lüllau Engineering Gmbh Method and device for irradiating irradiation of curved surfaces with non-ionizing radiation
CA2794121C (en) 2010-03-23 2016-10-11 Edwards Lifesciences Corporation Methods of conditioning sheet bioprosthetic tissue
FR2966740B1 (en) * 2010-10-27 2013-07-12 Biolux Medical Method and photo-modulation device
US8951266B2 (en) 2011-01-07 2015-02-10 Restoration Robotics, Inc. Methods and systems for modifying a parameter of an automated procedure
CN102670302B (en) * 2011-03-15 2015-01-28 明达医学科技股份有限公司 Optical apparatus and operating method thereof
US9314301B2 (en) 2011-08-01 2016-04-19 Miramar Labs, Inc. Applicator and tissue interface module for dermatological device
GB201120381D0 (en) * 2011-11-25 2012-01-11 Cyden Ltd Skin treatment apparatus
KR101219682B1 (en) * 2012-03-09 2013-01-15 (주)서울오션아쿠아리움 Laser irradiating system and laser irradiating robot comprising the same
US9211214B2 (en) * 2012-03-21 2015-12-15 Valeant Pharmaceuticals International, Inc Photodynamic therapy laser
US9040921B2 (en) 2012-07-28 2015-05-26 Harvard Apparatus Regenerative Technology, Inc. Analytical methods
EP3125837A4 (en) * 2014-04-04 2017-11-08 Aesthetics Biomedical Inc System and method for providing treatment feedback for a thermal treatment device
WO2014168832A1 (en) * 2013-04-08 2014-10-16 Farhan Taghizadeh System and method for providing treatment feedback for a thermal treatment device

Citations (62)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3307553A (en) 1963-01-30 1967-03-07 Edwin J Liebner Apparatus for cooling irradiated skin areas
US3821510A (en) 1973-02-22 1974-06-28 H Muncheryan Hand held laser instrumentation device
US4140130A (en) 1977-05-31 1979-02-20 Storm Iii Frederick K Electrode structure for radio frequency localized heating of tumor bearing tissue
US4587396A (en) 1982-12-31 1986-05-06 Laser Industries Ltd. Control apparatus particularly useful for controlling a laser
WO1986006527A1 (en) 1985-04-22 1986-11-06 The Quantum Fund Ltd. Skin-pattern recognition method and device
US4849859A (en) * 1986-04-22 1989-07-18 Kabushiki Kaisha Morita Seisakusho Laser-type handpiece
US4854320A (en) 1983-10-06 1989-08-08 Laser Surgery Software, Inc. Laser healing method and apparatus
US4913132A (en) * 1986-07-25 1990-04-03 Noble Gabriel Myringotomy instrument
DE3837248A1 (en) * 1988-10-28 1990-05-03 Teichmann Heinrich Otto Dr Phy Device for treating skin lesions
US4938205A (en) 1988-05-27 1990-07-03 The University Of Connecticut Endoscope with traced raster and elemental photodetectors
US5048904A (en) 1990-07-06 1991-09-17 General Scanning, Inc. Two-mirror scanner with pincushion error correction
US5106387A (en) 1985-03-22 1992-04-21 Massachusetts Institute Of Technology Method for spectroscopic diagnosis of tissue
US5107516A (en) 1990-02-15 1992-04-21 Laser-Laboratorium Apparatus for controlled ablation by laser radiation
WO1993008877A1 (en) 1991-11-06 1993-05-13 Lai Shui T Corneal surgery device and method
WO1993016631A1 (en) 1992-02-27 1993-09-02 Phoenix Laser Systems, Inc. Automated laser workstation for high precision surgical and industrial interventions
WO1994000194A1 (en) * 1992-06-29 1994-01-06 Raimund Kaufmann Probe for heating body tissue
US5330519A (en) 1990-09-05 1994-07-19 Breg, Inc. Therapeutic nonambient temperature fluid circulation system
US5344418A (en) 1991-12-12 1994-09-06 Shahriar Ghaffari Optical system for treatment of vascular lesions
US5382770A (en) 1993-01-14 1995-01-17 Reliant Laser Corporation Mirror-based laser-processing system with visual tracking and position control of a moving laser spot
WO1995003089A1 (en) 1993-07-21 1995-02-02 Lucid Technologies, Inc. Laser treatment system with electronic visualization
US5405368A (en) 1992-10-20 1995-04-11 Esc Inc. Method and apparatus for therapeutic electromagnetic treatment
US5456260A (en) 1994-04-05 1995-10-10 The General Hospital Corporation Fluorescence detection of cell proliferation
US5474549A (en) * 1991-07-09 1995-12-12 Laserscope Method and system for scanning a laser beam for controlled distribution of laser dosage
US5531740A (en) * 1994-09-06 1996-07-02 Rapistan Demag Corporation Automatic color-activated scanning treatment of dermatological conditions by laser
WO1996025979A1 (en) * 1995-02-24 1996-08-29 Grigory Borisovich Altshuler Device for use in the laser treatment of biological tissue (variants thereof)
US5588428A (en) 1993-04-28 1996-12-31 The University Of Akron Method and apparatus for non-invasive volume and texture analysis
EP0763371A2 (en) * 1995-09-15 1997-03-19 ESC Medical Systems Ltd. Method and apparatus for skin rejuvenation and wrinkle smoothing
US5620478A (en) 1992-10-20 1997-04-15 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5628744A (en) * 1993-12-21 1997-05-13 Laserscope Treatment beam handpiece
US5630811A (en) 1996-03-25 1997-05-20 Miller; Iain D. Method and apparatus for hair removal
EP0783904A2 (en) * 1995-12-26 1997-07-16 ESC Medical Systems Ltd. Method and apparatus for controlling the thermal profile of skin
EP0788765A1 (en) * 1996-02-09 1997-08-13 ESC Medical Systems Ltd. Method and apparatus for diagnosis of skin lesions
US5720772A (en) 1992-10-20 1998-02-24 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
EP0827716A2 (en) * 1996-09-04 1998-03-11 ESC Medical Systems Ltd. Device for cooling skin during laser treatment
US5735276A (en) 1995-03-21 1998-04-07 Lemelson; Jerome Method and apparatus for scanning and evaluating matter
US5742392A (en) 1996-04-16 1998-04-21 Seymour Light, Inc. Polarized material inspection apparatus
US5743902A (en) * 1995-01-23 1998-04-28 Coherent, Inc. Hand-held laser scanner
WO1998024514A1 (en) * 1996-12-02 1998-06-11 Palomar Medical Technologies Inc. Laser dermatology with feedback control
WO1998025528A1 (en) * 1996-12-10 1998-06-18 Asah Medico A/S An apparatus for cosmetic tissue treatment
US5779702A (en) * 1997-04-09 1998-07-14 Microaire Surgical Instruments, Inc. High speed pulse lavage surgical hand tool attachment
WO1998033558A1 (en) 1997-02-05 1998-08-06 Candela Corporation Method and apparatus for treating wrinkles in skin using radiation
US5814040A (en) * 1994-04-05 1998-09-29 The Regents Of The University Of California Apparatus and method for dynamic cooling of biological tissues for thermal mediated surgery
US5814041A (en) 1992-03-20 1998-09-29 The General Hospital Corporation Laser illuminator
US5820626A (en) 1996-07-30 1998-10-13 Laser Aesthetics, Inc. Cooling laser handpiece with refillable coolant reservoir
US5830208A (en) 1997-01-31 1998-11-03 Laserlite, Llc Peltier cooled apparatus and methods for dermatological treatment
WO1998049963A1 (en) 1997-05-08 1998-11-12 Laser Industries Ltd. Method and apparatus for performing transmyocardial revascularization
US5836939A (en) * 1995-10-25 1998-11-17 Plc Medical Systems, Inc. Surgical laser handpiece
WO1998051235A1 (en) 1997-05-15 1998-11-19 Palomar Medical Technologies, Inc. Method and apparatus for dermatology treatment
EP0880941A1 (en) 1997-05-30 1998-12-02 Nidek Co., Ltd. Laser treatment apparatus
WO1998055180A1 (en) 1997-06-06 1998-12-10 The Regents Of The University Of California Method and apparatus for causing rapid and deep spatially selective coagulation during thermally mediated therapeutic procedures
US5851181A (en) 1996-08-30 1998-12-22 Esc Medical Systems Ltd. Apparatus for simultaneously viewing and spectrally analyzing a portion of skin
WO1998057588A1 (en) 1997-06-17 1998-12-23 Cool Laser Optics, Inc. Method and apparatus for temperature control of biologic tissue with simultaneous irradiation
US5860968A (en) * 1995-11-03 1999-01-19 Luxar Corporation Laser scanning method and apparatus
US5865828A (en) 1997-08-08 1999-02-02 Jeng; James C. Coaxial dual laser
US5868732A (en) 1996-05-12 1999-02-09 Esc Medical Systems, Ltd. Cooling apparatus for cutaneous treatment employing a laser and method for operating same
US5868731A (en) 1996-03-04 1999-02-09 Innotech Usa, Inc. Laser surgical device and method of its use
EP0898983A1 (en) 1997-08-29 1999-03-03 Nidek Co., Ltd. Laser treatment apparatus
WO1999017668A1 (en) 1997-10-08 1999-04-15 The General Hospital Corporation Phototherapy methods and systems
EP0933096A2 (en) 1998-01-29 1999-08-04 International Business Machines Corporation Laser for dermal ablation
WO1999046005A1 (en) 1998-03-12 1999-09-16 Palomar Medical Technologies, Inc. System for electromagnetic radiation of the skin
US5995867A (en) 1997-03-19 1999-11-30 Lucid Inc Cellular surgery utilizing confocal microscopy
US6110195A (en) 1998-06-01 2000-08-29 Altralight, Inc. Method and apparatus for surgical and dermatological treatment by multi-wavelength laser light

Family Cites Families (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5486172A (en) 1989-05-30 1996-01-23 Chess; Cyrus Apparatus for treating cutaneous vascular lesions
US5057104A (en) 1989-05-30 1991-10-15 Cyrus Chess Method and apparatus for treating cutaneous vascular lesions
DE4238457A1 (en) 1992-11-13 1994-05-19 Coiffeur Consulting Team Elect Procedures for acting on hair for cosmetic purposes
CA2131750C (en) 1994-07-26 2000-11-21 Thermolase Corporation Improved hair removal method
US5595568A (en) 1995-02-01 1997-01-21 The General Hospital Corporation Permanent hair removal using optical pulses
US6162211A (en) * 1996-12-05 2000-12-19 Thermolase Corporation Skin enhancement using laser light
US6096029A (en) 1997-02-24 2000-08-01 Laser Skin Toner, Inc. Laser method for subsurface cutaneous treatment
US6008889A (en) 1997-04-16 1999-12-28 Zeng; Haishan Spectrometer system for diagnosis of skin disease
US6074382A (en) * 1997-08-29 2000-06-13 Asah Medico A/S Apparatus for tissue treatment
DE19852948C2 (en) 1998-11-12 2002-07-18 Asclepion Meditec Ag Dermatological hand piece

Patent Citations (68)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3307553A (en) 1963-01-30 1967-03-07 Edwin J Liebner Apparatus for cooling irradiated skin areas
US3821510A (en) 1973-02-22 1974-06-28 H Muncheryan Hand held laser instrumentation device
US4140130A (en) 1977-05-31 1979-02-20 Storm Iii Frederick K Electrode structure for radio frequency localized heating of tumor bearing tissue
US4587396A (en) 1982-12-31 1986-05-06 Laser Industries Ltd. Control apparatus particularly useful for controlling a laser
US4854320A (en) 1983-10-06 1989-08-08 Laser Surgery Software, Inc. Laser healing method and apparatus
US5106387A (en) 1985-03-22 1992-04-21 Massachusetts Institute Of Technology Method for spectroscopic diagnosis of tissue
WO1986006527A1 (en) 1985-04-22 1986-11-06 The Quantum Fund Ltd. Skin-pattern recognition method and device
US4849859A (en) * 1986-04-22 1989-07-18 Kabushiki Kaisha Morita Seisakusho Laser-type handpiece
US4913132A (en) * 1986-07-25 1990-04-03 Noble Gabriel Myringotomy instrument
US4938205A (en) 1988-05-27 1990-07-03 The University Of Connecticut Endoscope with traced raster and elemental photodetectors
DE3837248A1 (en) * 1988-10-28 1990-05-03 Teichmann Heinrich Otto Dr Phy Device for treating skin lesions
US5107516A (en) 1990-02-15 1992-04-21 Laser-Laboratorium Apparatus for controlled ablation by laser radiation
US5048904A (en) 1990-07-06 1991-09-17 General Scanning, Inc. Two-mirror scanner with pincushion error correction
US5330519B1 (en) 1990-09-05 1998-11-10 Breg Inc Therapeutic nonambient temperature fluid circulation system
US5330519A (en) 1990-09-05 1994-07-19 Breg, Inc. Therapeutic nonambient temperature fluid circulation system
US5474549A (en) * 1991-07-09 1995-12-12 Laserscope Method and system for scanning a laser beam for controlled distribution of laser dosage
WO1993008877A1 (en) 1991-11-06 1993-05-13 Lai Shui T Corneal surgery device and method
US5344418A (en) 1991-12-12 1994-09-06 Shahriar Ghaffari Optical system for treatment of vascular lesions
WO1993016631A1 (en) 1992-02-27 1993-09-02 Phoenix Laser Systems, Inc. Automated laser workstation for high precision surgical and industrial interventions
US5814041A (en) 1992-03-20 1998-09-29 The General Hospital Corporation Laser illuminator
WO1994000194A1 (en) * 1992-06-29 1994-01-06 Raimund Kaufmann Probe for heating body tissue
US5405368A (en) 1992-10-20 1995-04-11 Esc Inc. Method and apparatus for therapeutic electromagnetic treatment
US5620478A (en) 1992-10-20 1997-04-15 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5720772A (en) 1992-10-20 1998-02-24 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5382770A (en) 1993-01-14 1995-01-17 Reliant Laser Corporation Mirror-based laser-processing system with visual tracking and position control of a moving laser spot
US5588428A (en) 1993-04-28 1996-12-31 The University Of Akron Method and apparatus for non-invasive volume and texture analysis
WO1995003089A1 (en) 1993-07-21 1995-02-02 Lucid Technologies, Inc. Laser treatment system with electronic visualization
US5653706A (en) * 1993-07-21 1997-08-05 Lucid Technologies Inc. Dermatological laser treatment system with electronic visualization of the area being treated
US5628744A (en) * 1993-12-21 1997-05-13 Laserscope Treatment beam handpiece
US5456260A (en) 1994-04-05 1995-10-10 The General Hospital Corporation Fluorescence detection of cell proliferation
US5814040A (en) * 1994-04-05 1998-09-29 The Regents Of The University Of California Apparatus and method for dynamic cooling of biological tissues for thermal mediated surgery
US5531740A (en) * 1994-09-06 1996-07-02 Rapistan Demag Corporation Automatic color-activated scanning treatment of dermatological conditions by laser
US5957915A (en) 1995-01-23 1999-09-28 Coherent, Inc. Hand-held laser scanner
US5743902A (en) * 1995-01-23 1998-04-28 Coherent, Inc. Hand-held laser scanner
WO1996025979A1 (en) * 1995-02-24 1996-08-29 Grigory Borisovich Altshuler Device for use in the laser treatment of biological tissue (variants thereof)
US5735276A (en) 1995-03-21 1998-04-07 Lemelson; Jerome Method and apparatus for scanning and evaluating matter
EP0763371A2 (en) * 1995-09-15 1997-03-19 ESC Medical Systems Ltd. Method and apparatus for skin rejuvenation and wrinkle smoothing
US5836939A (en) * 1995-10-25 1998-11-17 Plc Medical Systems, Inc. Surgical laser handpiece
US5860968A (en) * 1995-11-03 1999-01-19 Luxar Corporation Laser scanning method and apparatus
EP0783904A2 (en) * 1995-12-26 1997-07-16 ESC Medical Systems Ltd. Method and apparatus for controlling the thermal profile of skin
EP0788765A1 (en) * 1996-02-09 1997-08-13 ESC Medical Systems Ltd. Method and apparatus for diagnosis of skin lesions
US5833612A (en) 1996-02-09 1998-11-10 Esc Medical Systems, Ltd. Method and apparatus for diagnosis skin lesions
US5868731A (en) 1996-03-04 1999-02-09 Innotech Usa, Inc. Laser surgical device and method of its use
US5630811A (en) 1996-03-25 1997-05-20 Miller; Iain D. Method and apparatus for hair removal
US5853407A (en) 1996-03-25 1998-12-29 Luxar Corporation Method and apparatus for hair removal
US5742392A (en) 1996-04-16 1998-04-21 Seymour Light, Inc. Polarized material inspection apparatus
US5868732A (en) 1996-05-12 1999-02-09 Esc Medical Systems, Ltd. Cooling apparatus for cutaneous treatment employing a laser and method for operating same
US5820626A (en) 1996-07-30 1998-10-13 Laser Aesthetics, Inc. Cooling laser handpiece with refillable coolant reservoir
US5851181A (en) 1996-08-30 1998-12-22 Esc Medical Systems Ltd. Apparatus for simultaneously viewing and spectrally analyzing a portion of skin
EP0827716A2 (en) * 1996-09-04 1998-03-11 ESC Medical Systems Ltd. Device for cooling skin during laser treatment
WO1998024514A1 (en) * 1996-12-02 1998-06-11 Palomar Medical Technologies Inc. Laser dermatology with feedback control
WO1998025528A1 (en) * 1996-12-10 1998-06-18 Asah Medico A/S An apparatus for cosmetic tissue treatment
US5830208A (en) 1997-01-31 1998-11-03 Laserlite, Llc Peltier cooled apparatus and methods for dermatological treatment
WO1998033558A1 (en) 1997-02-05 1998-08-06 Candela Corporation Method and apparatus for treating wrinkles in skin using radiation
US5810801A (en) 1997-02-05 1998-09-22 Candela Corporation Method and apparatus for treating wrinkles in skin using radiation
US5995867A (en) 1997-03-19 1999-11-30 Lucid Inc Cellular surgery utilizing confocal microscopy
US5779702A (en) * 1997-04-09 1998-07-14 Microaire Surgical Instruments, Inc. High speed pulse lavage surgical hand tool attachment
WO1998049963A1 (en) 1997-05-08 1998-11-12 Laser Industries Ltd. Method and apparatus for performing transmyocardial revascularization
WO1998051235A1 (en) 1997-05-15 1998-11-19 Palomar Medical Technologies, Inc. Method and apparatus for dermatology treatment
EP0880941A1 (en) 1997-05-30 1998-12-02 Nidek Co., Ltd. Laser treatment apparatus
WO1998055180A1 (en) 1997-06-06 1998-12-10 The Regents Of The University Of California Method and apparatus for causing rapid and deep spatially selective coagulation during thermally mediated therapeutic procedures
WO1998057588A1 (en) 1997-06-17 1998-12-23 Cool Laser Optics, Inc. Method and apparatus for temperature control of biologic tissue with simultaneous irradiation
US5865828A (en) 1997-08-08 1999-02-02 Jeng; James C. Coaxial dual laser
EP0898983A1 (en) 1997-08-29 1999-03-03 Nidek Co., Ltd. Laser treatment apparatus
WO1999017668A1 (en) 1997-10-08 1999-04-15 The General Hospital Corporation Phototherapy methods and systems
EP0933096A2 (en) 1998-01-29 1999-08-04 International Business Machines Corporation Laser for dermal ablation
WO1999046005A1 (en) 1998-03-12 1999-09-16 Palomar Medical Technologies, Inc. System for electromagnetic radiation of the skin
US6110195A (en) 1998-06-01 2000-08-29 Altralight, Inc. Method and apparatus for surgical and dermatological treatment by multi-wavelength laser light

Cited By (75)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8328794B2 (en) 1996-12-02 2012-12-11 Palomar Medical Technologies, Inc. System for electromagnetic radiation dermatology and head for use therewith
US20050171517A1 (en) * 1996-12-02 2005-08-04 Palomar Medical Technologies, Inc. System for electromagnetic radiation dermatology and head for use therewith
US7935107B2 (en) 1997-05-15 2011-05-03 Palomar Medical Technologies, Inc. Heads for dermatology treatment
US8109924B2 (en) 1997-05-15 2012-02-07 Palomar Medical Technologies, Inc. Heads for dermatology treatment
US7763016B2 (en) 1997-05-15 2010-07-27 Palomar Medical Technologies, Inc. Light energy delivery head
US7758621B2 (en) 1997-05-15 2010-07-20 Palomar Medical Technologies, Inc. Method and apparatus for therapeutic EMR treatment on the skin
US8002768B1 (en) 1997-05-15 2011-08-23 Palomar Medical Technologies, Inc. Light energy delivery head
US8328796B2 (en) 1997-05-15 2012-12-11 Palomar Medical Technologies, Inc. Light energy delivery head
US8182473B2 (en) 1999-01-08 2012-05-22 Palomar Medical Technologies Cooling system for a photocosmetic device
US8287524B2 (en) * 2001-08-23 2012-10-16 Jerry Siegel Apparatus and method for performing radiation energy treatments
US20070106284A1 (en) * 2001-08-23 2007-05-10 Jerry Siegel Apparatus and method for performing radiation energy treatments
US7942916B2 (en) 2002-05-23 2011-05-17 Palomar Medical Technologies, Inc. Phototreatment device for use with coolants and topical substances
US7942915B2 (en) 2002-05-23 2011-05-17 Palomar Medical Technologies, Inc. Phototreatment device for use with coolants
US8915948B2 (en) 2002-06-19 2014-12-23 Palomar Medical Technologies, Llc Method and apparatus for photothermal treatment of tissue at depth
US20060089687A1 (en) * 2002-12-12 2006-04-27 Greg Spooner System for controlled spatially-selective epidermal pigmentation phototherapy with UVA LEDs
US20040143278A1 (en) * 2003-01-17 2004-07-22 Nova-Tech Engineering, Inc. Apparatus and method for upper and lower beak treatment
US7232450B2 (en) * 2003-01-17 2007-06-19 Nova-Tech Engineering, Inc. Apparatus and method for upper and lower beak treatment
US20050154380A1 (en) * 2003-12-23 2005-07-14 Debenedictis Leonard C. Method and apparatus for monitoring and controlling laser-induced tissue treatment
US7282060B2 (en) * 2003-12-23 2007-10-16 Reliant Technologies, Inc. Method and apparatus for monitoring and controlling laser-induced tissue treatment
US20060119920A1 (en) * 2003-12-31 2006-06-08 Debenedictis Leonard C High speed, high efficiency optical pattern generator using rotating optical elements
US20060217695A1 (en) * 2003-12-31 2006-09-28 Debenedictis Leonard C Optically-induced treatment of internal tissue
US20050285928A1 (en) * 2003-12-31 2005-12-29 Broome Barry G Optical pattern generator using a single rotating component
US7265884B2 (en) 2003-12-31 2007-09-04 Reliant Technologies, Inc. High speed, high efficiency optical pattern generator using rotating optical elements
US9452013B2 (en) 2004-04-01 2016-09-27 The General Hospital Corporation Apparatus for dermatological treatment using chromophores
US8268332B2 (en) 2004-04-01 2012-09-18 The General Hospital Corporation Method for dermatological treatment using chromophores
US9173837B2 (en) 2004-04-19 2015-11-03 The Invention Science Fund I, Llc Controllable release nasal system
US9011329B2 (en) 2004-04-19 2015-04-21 Searete Llc Lumenally-active device
US9801527B2 (en) 2004-04-19 2017-10-31 Gearbox, Llc Lumen-traveling biological interface device
US7722656B1 (en) 2005-02-25 2010-05-25 Kim Robin Segal Device and method for stimulating hair growth
US20070060984A1 (en) * 2005-09-09 2007-03-15 Webb James S Apparatus and method for optical stimulation of nerves and other animal tissue
US8985119B1 (en) 2005-09-09 2015-03-24 Lockheed Martin Corporation Method and apparatus for optical stimulation of nerves and other animal tissue
US7736382B2 (en) * 2005-09-09 2010-06-15 Lockheed Martin Corporation Apparatus for optical stimulation of nerves and other animal tissue
US8346347B2 (en) 2005-09-15 2013-01-01 Palomar Medical Technologies, Inc. Skin optical characterization device
US8956396B1 (en) 2005-10-24 2015-02-17 Lockheed Martin Corporation Eye-tracking visual prosthetic and method
US8945197B1 (en) 2005-10-24 2015-02-03 Lockheed Martin Corporation Sight-restoring visual prosthetic and method using infrared nerve-stimulation light
US8929973B1 (en) 2005-10-24 2015-01-06 Lockheed Martin Corporation Apparatus and method for characterizing optical sources used with human and animal tissues
US20070239142A1 (en) * 2006-03-10 2007-10-11 Palomar Medical Technologies, Inc. Photocosmetic device
US20080058795A1 (en) * 2006-04-12 2008-03-06 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Systems for autofluorescent imaging and target ablation
US9408530B2 (en) 2006-04-12 2016-08-09 Gearbox, Llc Parameter-based navigation by a lumen traveling device
US9198563B2 (en) 2006-04-12 2015-12-01 The Invention Science Fund I, Llc Temporal control of a lumen traveling device in a body tube tree
US9220917B2 (en) * 2006-04-12 2015-12-29 The Invention Science Fund I, Llc Systems for autofluorescent imaging and target ablation
US8251982B2 (en) * 2006-04-14 2012-08-28 Asa S.R.L. Laser apparatus for therapeutic applications
US20070244526A1 (en) * 2006-04-14 2007-10-18 Asa S.R.L. Laser apparatus for therapeutic applications
US9028536B2 (en) 2006-08-02 2015-05-12 Cynosure, Inc. Picosecond laser apparatus and methods for its operation and use
US8506613B2 (en) 2006-09-21 2013-08-13 Lockheed Martin Corporation Miniature method and apparatus for optical stimulation of nerves and other animal tissue
US20080077198A1 (en) * 2006-09-21 2008-03-27 Aculight Corporation Miniature apparatus and method for optical stimulation of nerves and other animal tissue
US7988688B2 (en) 2006-09-21 2011-08-02 Lockheed Martin Corporation Miniature apparatus and method for optical stimulation of nerves and other animal tissue
US9061135B1 (en) 2006-09-28 2015-06-23 Lockheed Martin Corporation Apparatus and method for managing chronic pain with infrared and low-level light sources
US8996131B1 (en) 2006-09-28 2015-03-31 Lockheed Martin Corporation Apparatus and method for managing chronic pain with infrared light sources and heat
US20080147053A1 (en) * 2006-12-15 2008-06-19 Korea Electro Technology Research Institute Apparatus and method for photodynamic diagnosis and therapy of skin diseases and light source system thereof
US8496695B2 (en) * 2006-12-15 2013-07-30 Korea Electro Technology Research Institute Apparatus and method for photodynamic diagnosis and therapy of skin diseases and light source system thereof
US8551150B1 (en) 2007-01-11 2013-10-08 Lockheed Martin Corporation Method and system for optical stimulation of nerves
US8317848B1 (en) 2007-01-11 2012-11-27 Lockheed Martin Corporation Vestibular implant and method for optical stimulation of nerves
US8012189B1 (en) 2007-01-11 2011-09-06 Lockheed Martin Corporation Method and vestibular implant using optical stimulation of nerves
US7883536B1 (en) 2007-01-19 2011-02-08 Lockheed Martin Corporation Hybrid optical-electrical probes
US8632577B1 (en) 2007-01-19 2014-01-21 Lockheed Martin Corporation Hybrid optical-electrical probes for stimulation of nerve or other animal tissue
US8357187B1 (en) 2007-01-19 2013-01-22 Lockheed Martin Corporation Hybrid optical-electrical probes for stimulation of nerve or other animal tissue
US8475506B1 (en) 2007-08-13 2013-07-02 Lockheed Martin Corporation VCSEL array stimulator apparatus and method for light stimulation of bodily tissues
US9011508B2 (en) 2007-11-30 2015-04-21 Lockheed Martin Corporation Broad wavelength profile to homogenize the absorption profile in optical stimulation of nerves
US9011509B2 (en) 2007-11-30 2015-04-21 Lockheed Martin Corporation Individually optimized performance of optically stimulating cochlear implants
US8998914B2 (en) 2007-11-30 2015-04-07 Lockheed Martin Corporation Optimized stimulation rate of an optically stimulating cochlear implant
US8160696B2 (en) 2008-10-03 2012-04-17 Lockheed Martin Corporation Nerve stimulator and method using simultaneous electrical and optical signals
US8498699B2 (en) 2008-10-03 2013-07-30 Lockheed Martin Company Method and nerve stimulator using simultaneous electrical and optical signals
US8744570B2 (en) 2009-01-23 2014-06-03 Lockheed Martin Corporation Optical stimulation of the brainstem and/or midbrain, including auditory areas
US20110087310A1 (en) * 2009-10-12 2011-04-14 Wellmike Enterprise Co., Ltd. Hair-growth caring apparatus
US8968376B2 (en) 2010-05-28 2015-03-03 Lockheed Martin Corporation Nerve-penetrating apparatus and method for optical and/or electrical nerve stimulation of peripheral nerves
US8792978B2 (en) 2010-05-28 2014-07-29 Lockheed Martin Corporation Laser-based nerve stimulators for, E.G., hearing restoration in cochlear prostheses and method
US8864806B2 (en) 2010-05-28 2014-10-21 Lockheed Martin Corporation Optical bundle apparatus and method for optical and/or electrical nerve stimulation of peripheral nerves
US8652187B2 (en) 2010-05-28 2014-02-18 Lockheed Martin Corporation Cuff apparatus and method for optical and/or electrical nerve stimulation of peripheral nerves
US8747447B2 (en) 2011-07-22 2014-06-10 Lockheed Martin Corporation Cochlear implant and method enabling enhanced music perception
US8840654B2 (en) 2011-07-22 2014-09-23 Lockheed Martin Corporation Cochlear implant using optical stimulation with encoded information designed to limit heating effects
US8834545B2 (en) 2011-07-22 2014-09-16 Lockheed Martin Corporation Optical-stimulation cochlear implant with electrode(s) at the apical end for electrical stimulation of apical spiral ganglion cells of the cochlea
US8894697B2 (en) 2011-07-22 2014-11-25 Lockheed Martin Corporation Optical pulse-width modulation used in an optical-stimulation cochlear implant
US8709078B1 (en) 2011-08-03 2014-04-29 Lockheed Martin Corporation Ocular implant with substantially constant retinal spacing for transmission of nerve-stimulation light
US9780518B2 (en) 2012-04-18 2017-10-03 Cynosure, Inc. Picosecond laser apparatus and methods for treating target tissues with same

Also Published As

Publication number Publication date Type
US6676654B1 (en) 2004-01-13 grant
WO2000053261A1 (en) 2000-09-14 application

Similar Documents

Publication Publication Date Title
US6350261B1 (en) Selective laser-induced heating of biological tissue
US6086366A (en) Device for removing material from a workpiece by laser radiation
US7090670B2 (en) Multi-spot laser surgical apparatus and method
US5336217A (en) Process for treatment by irradiating an area of a body, and treatment apparatus usable in dermatology for the treatment of cutaneous angio dysplasias
US6579283B1 (en) Apparatus and method employing a single laser for removal of hair, veins and capillaries
US4848340A (en) Eyetracker and method of use
US5921981A (en) Multi-spot laser surgery
US5334191A (en) Laser tissue welding control system
US4901718A (en) 3-Dimensional laser beam guidance system
US6210401B1 (en) Method of, and apparatus for, surgery of the cornea
US5643249A (en) Optical ophthalmic treatment apparatus
US6475138B1 (en) Apparatus and method as preparation for performing a myringotomy in a child's ear without the need for anaesthesia
US4316467A (en) Control for laser hemangioma treatment system
US20070129709A1 (en) System and method for minimally traumatic ophthalmic photomedicine
US6004314A (en) Optical coherence tomography assisted surgical apparatus
US5147349A (en) Diode laser device for photocoagulation of the retina
US6529543B1 (en) Apparatus for controlling laser penetration depth
US4719912A (en) Apparatus for controlling the photocoagulation of biological tissue
US4750486A (en) Apparatus for moving a mirror
US6695835B2 (en) Laser treatment apparatus
US5125922A (en) Method for laser surgery
US7309335B2 (en) Dermatological treatment with visualization
US6149644A (en) Method and apparatus for epidermal treatment with computer controlled moving focused infrared light
US20010053907A1 (en) Laser treatment apparatus
US5628744A (en) Treatment beam handpiece

Legal Events

Date Code Title Description
FPAY Fee payment

Year of fee payment: 8

FPAY Fee payment

Year of fee payment: 12

SULP Surcharge for late payment

Year of fee payment: 11

AS Assignment

Owner name: MEDART A/S, DENMARK

Free format text: CHANGE OF NAME;ASSIGNOR:ASAH MEDICO A/S;REEL/FRAME:029700/0667

Effective date: 20130107