CA2323479A1 - System for electromagnetic radiation of the skin - Google Patents
System for electromagnetic radiation of the skin Download PDFInfo
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- CA2323479A1 CA2323479A1 CA002323479A CA2323479A CA2323479A1 CA 2323479 A1 CA2323479 A1 CA 2323479A1 CA 002323479 A CA002323479 A CA 002323479A CA 2323479 A CA2323479 A CA 2323479A CA 2323479 A1 CA2323479 A1 CA 2323479A1
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- Prior art keywords
- skin
- waveguide
- head
- patient
- radiation
- 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.)
- Abandoned
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Classifications
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- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
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- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/203—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser applying laser energy to the outside of the body
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- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
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Landscapes
- Health & Medical Sciences (AREA)
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Abstract
A system for treating a selected dermatologic problem and a head for use with such system are provided. The head may include an optical waveguide having a first end to which EM radiation appropriate for treating the condition is applied. The waveguide also has a skin-contacting second end opposite the first end, a temperature sensor being located within a few millimeters, and preferably within 1 to 2 millimeters, of the second end of the waveguide. A temperature sensor may be similarly located in other skin contacting portions of the head. A mechanism is preferably also provided for removing heat from the waveguide and, for preferred embodiments, the second end of the head which is in contact with the skin has a reflection aperture which is substantially as great as the radiation back-scatter aperture from the patient's skin. Such aperture may be the aperture at the second end of the waveguide or a reflection plate or surface of appropriate size may surround the waveguide or other light path at its second end. The portion of the back-scattered radiation entering the waveguide is substantially internally reflected therein, with a reflector being provided, preferably at the first end of the waveguide, for returning back-scattered light to the patient's skin. The reflector may be angle dependent so as to more strongly reflect back-scattered light more perpendicular to the skin surface than back-scattered radiation more parallel to the skin surface. Controls are also provided responsive to the temperature sensing for determining temperature at a predetermined depth in the patient's skin, for example at the DE junction, and for utilizing this information to detect good thermal contact between the head and the patient's skin and to otherwise control treatment. The head may also have a mechanism for forming a reflecting chamber under the waveguide and drawing a fold of skin therein, or for providing a second enlarged waveguide to expand the optical aperture of the radiation.
Description
WO 99146005 PG"T/US99/05501 SYSTEM FOR ELECTROMAGNETIC RADIATION OF THE SKIN
Related Annlications This application is a continuation in part of application Serial No.
08/759,036, and of application Serial No. 08/759,136, both filed December 2, 1996. and of application Serial No.
09/078,055, filed May 13, 1998 and claims priority of provision application No. 60/077,794 and provisional application No. 60/115,447, filed January 8, 1999, which applications are all incorporated herein by reference.
Field of the Invention This invention relates to the utilization of electromagnetic (EM) radiation for treating selected dermatologic problems, and more particularly to a system which utilizes temperature detection at a waveguide though which radiation is being applied to the patient's skin to perform ~ 5 various control functions and to a head usable in such system or elsewhere, which head includes efficient reflectors for back-scattered radiation and/or for otherwise enhancing irradiation of a target volume containing the dermatologic problem.
Background of the Invention Lasers, lamps and other sources of electromagnetic radiation are being increasingly utilized to treat various dermatological conditions, and in particular for the removal of unwanted hail, spider veins, leg veins, other veins or blood vessels which are visible through the patient's skin, lesions, port-wine stains, tattoos and the like. One problem with such treatments is that the only way to get the radiation to a target volume in the dermis where treatment is desired is to z5 transmit the radiation to such volume through the overlying epidermis.
Further, since many of the treatments involve absorption of energy by melanin in the dermal volume being treated, for example in a hair follicle, and there is also melanin in the epidermis.
particularly in the portion thereof at the dermal/epidermal (DE) junction, the EM radiation used for treatment is generally also absorbed to varying degrees in the epidermis. Further. the deeper in the dermis the treatment 3o is desired and/or the larger the element being treated. the more energy must be used, this generally involving use of a more powerful laser or other radiation source with higher fluence and/or operating such source for longer time durations. However. as the energy applied through the epidermis increases, the potential for damage to the epidermis as a result of energy absorption therein also increases.
Therefore, one limitation on the energies which can be used for various dermatological treatments in the dermis, and in particular on the depths in the dermis at which treatment can be performed, and on the size of the elements which can be treated, is that the energy applied cannot be so high as to cause appreciable damage to the epidermis. Various ways around this problem have been proposed in the prior art, most of which involve some cooling of the epidermis prior to and/or during treatment to limit or prevent thermal damage thereto.
Examples of such procedures include applying cryogenic or other cooling sprays to the skin, applying a cooling gel 1 o to the skin, applying radiation through a cold-pack in contact with the skin or through an applicator which is cooled by flowing water, flowing air, or the like.
However, these prior art systems have not been wholly satisfactory. One reason for this is that, since most of the absorption is in the melanin located in the lower portions of the epidermis, it is desirable to have cooling through the entire epidermal layer, which is typically about 0.1 mm thick. However, it ~ 5 is not desirable that the cooling extend significantly below the DE
junction into the dermal layer since cooling in the dermal layer can potentially inhibit the desired thermal damage to follicles, blood vessels or the like in this region. Further, there are significant variations in radiation absorption by a patients skin, not only among different individuals, people having darker skin absorbing more radiation and being more prone to epidermal damage than people with lighter 2o skin, but even for different areas on the body of a single individual.
Therefore. cooling which is not customized to the treatment area generally results in the cooling not being to the proper depth, a problem which can interfere with treatment and/or permit thermal damage to the epidermis.
It would therefore be desirable if the temperature at a selected depth in the skin, for 25 example the DE junction, could be measured, and this temperature utilized to control skin temperature. for example through the epidermis, by some combination of controlling the laser energy applied to skin and/or controlling cooling applied to the skin.
However, while infrared sensors have for example been utilized in the past to detect temperature at the surface of the skin.
such detection does not provide an accurate indication of temperature even at the skin surface.
3o these readings varying with such factors as skin layer thickness, skin roughness and skin color in addition to temperature. Infrared sensors also provide virtually no information as to skin temperature at a depth below the surface. Therefore, such detection has heretofore been used only for gross controls, for example to turn off the laser if an emergency temperature threshold is exceeded or the like, but not to fine tune energy application andlor cooling so as to maintain a desired temperature at a selected depth, for example at the DE junction, thereby facilitating a desired treatment without epidermal damage.
A need therefore exists for an improved technique which permits more accurate determinations of skin temperature at various depths, including at the DE
junction, so as to permit more accurate and more automatic control of EM radiation treatments for various dermatological conditions. In particular, because of variations in skin pigmentation, differences in epidermal depth, and other dermatological differences among patients, laser dermatology procedures are 1 o now performed almost exclusively by physicians or other highly trained individuals, and such individuals must exercise great care to assure that epidermal damage does not occur, while still achieving the desired therapeutic effect. More accurate measurement of temperature at desired depths would make treatments by such skilled personnel easier to perform and would permit such procedures to be safely performed by less highly trained, and therefore less expensive, personnel.
Such skin temperature measurements could also be utilized to determine skin type/pigmentation for the patient and/or for the part of a patient's body being treated and/or for other purposes.
Where cooling of the epidermis is achieved by placing a cooled applicator or other cooled body in contact with the patient's skin, the contact must be made with sufficient pressure to assure good thermal contact between the cooled body and the skin. However, differences in skin thickness and elasticity, differences in bone backing and other factors affect the pressure required to achieve good thermal contact for different patients and for different areas on the body for the same patient. This is another reason why highly trained and skilled individuals are required for performing the treatments and contributes to the high cost of the treatment.
It would therefore be preferable if an automatic technique could be provided for detecting, and thus assuring, good thermal contact between a cooling element and the patient's skin. Such a technique or mechanism, by assuring good thermal contact with the skin before the radiation source is fired, could solve two critical safety problems for radiation dermatology. First, it assures adequate cooling of the epidermis before heating thereof through energy absorption; and second, it assures that the radiation will not be accidentally applied to the eyes or other unwanted place.
3o Related but opposite problems arise in performing certain skin resurfacing/wrinkle removal procedures where the objective is to heat and destroy only the most surface layer of the skin, for example the epidermis, with miumal damage to underlying layers. This requires tight control of factors such as laser energy, pulse duration and repetition rate.
However, variations in patient's skin make such tight control difficult even for highly trained and skilled personnel.
Similar problems also arise in other dermatological procedures involving lasers or other radiation sources.
Another related problem in using an EM radiation source for dermatological treatment is that the skin reflects back a significant portion of the radiation applied thereto. Since this reflected energy does not reach the treatment site, a higher energy radiation source is required to achieve the desired dermatological treatment than would be the case if a larger percentage of the applied radiation reached the treatment site. It lias previously been suggested that one solution I o to this problem is to provide a retro-reflector which collects and returns such back-scattered radiation to the patient's skin. However, existing retro-reflector devices have not optimized the collection and return of such back-scattered radiation and improved techniques for the more efficient reutilization of back-scattered radiation is therefore desirable.
One particular problem with prior art retroreflectors is that they reflect all back-scattered radiation at substantially the same angle the radiation was received; however, radiation at an angle more parallel than perpendicular to the skin surface generally does not reach the treatment area and therefore only heats the surface of the skin, contributing to thermal damage of the skin, without having any beneficial/therapeutic effect. A retroreflection technique which does not contribute to or increase this "parallel" radiation would therefore be desirable.
2o Two other factors can contribute to the efficiency of dermatologic treatments. The first factor is "spot size" or in other words the optical aperture of the applied radiation. Spot size is typically limited by the optics of the handpiece utilized and by the desired fluence as a function of the available energy source. However, a larger spot size permits treatment of large body areas such as back or legs to be accomplished much more quickly, something which enhances both patient satisfaction and practitioner profitability. A technique for facilitating larger spot sizes is thus desirable.
Secondly, anything which reduces the distance from the irradiation source to the target area reduces the amount of energy required to achieve a desired therapeutic effect and anything which permits more of the applied energy to reach the target area has a similar effect. Techniques 3o which facilitate the achievements of these objectives are therefore also desirable.
Related Annlications This application is a continuation in part of application Serial No.
08/759,036, and of application Serial No. 08/759,136, both filed December 2, 1996. and of application Serial No.
09/078,055, filed May 13, 1998 and claims priority of provision application No. 60/077,794 and provisional application No. 60/115,447, filed January 8, 1999, which applications are all incorporated herein by reference.
Field of the Invention This invention relates to the utilization of electromagnetic (EM) radiation for treating selected dermatologic problems, and more particularly to a system which utilizes temperature detection at a waveguide though which radiation is being applied to the patient's skin to perform ~ 5 various control functions and to a head usable in such system or elsewhere, which head includes efficient reflectors for back-scattered radiation and/or for otherwise enhancing irradiation of a target volume containing the dermatologic problem.
Background of the Invention Lasers, lamps and other sources of electromagnetic radiation are being increasingly utilized to treat various dermatological conditions, and in particular for the removal of unwanted hail, spider veins, leg veins, other veins or blood vessels which are visible through the patient's skin, lesions, port-wine stains, tattoos and the like. One problem with such treatments is that the only way to get the radiation to a target volume in the dermis where treatment is desired is to z5 transmit the radiation to such volume through the overlying epidermis.
Further, since many of the treatments involve absorption of energy by melanin in the dermal volume being treated, for example in a hair follicle, and there is also melanin in the epidermis.
particularly in the portion thereof at the dermal/epidermal (DE) junction, the EM radiation used for treatment is generally also absorbed to varying degrees in the epidermis. Further. the deeper in the dermis the treatment 3o is desired and/or the larger the element being treated. the more energy must be used, this generally involving use of a more powerful laser or other radiation source with higher fluence and/or operating such source for longer time durations. However. as the energy applied through the epidermis increases, the potential for damage to the epidermis as a result of energy absorption therein also increases.
Therefore, one limitation on the energies which can be used for various dermatological treatments in the dermis, and in particular on the depths in the dermis at which treatment can be performed, and on the size of the elements which can be treated, is that the energy applied cannot be so high as to cause appreciable damage to the epidermis. Various ways around this problem have been proposed in the prior art, most of which involve some cooling of the epidermis prior to and/or during treatment to limit or prevent thermal damage thereto.
Examples of such procedures include applying cryogenic or other cooling sprays to the skin, applying a cooling gel 1 o to the skin, applying radiation through a cold-pack in contact with the skin or through an applicator which is cooled by flowing water, flowing air, or the like.
However, these prior art systems have not been wholly satisfactory. One reason for this is that, since most of the absorption is in the melanin located in the lower portions of the epidermis, it is desirable to have cooling through the entire epidermal layer, which is typically about 0.1 mm thick. However, it ~ 5 is not desirable that the cooling extend significantly below the DE
junction into the dermal layer since cooling in the dermal layer can potentially inhibit the desired thermal damage to follicles, blood vessels or the like in this region. Further, there are significant variations in radiation absorption by a patients skin, not only among different individuals, people having darker skin absorbing more radiation and being more prone to epidermal damage than people with lighter 2o skin, but even for different areas on the body of a single individual.
Therefore. cooling which is not customized to the treatment area generally results in the cooling not being to the proper depth, a problem which can interfere with treatment and/or permit thermal damage to the epidermis.
It would therefore be desirable if the temperature at a selected depth in the skin, for 25 example the DE junction, could be measured, and this temperature utilized to control skin temperature. for example through the epidermis, by some combination of controlling the laser energy applied to skin and/or controlling cooling applied to the skin.
However, while infrared sensors have for example been utilized in the past to detect temperature at the surface of the skin.
such detection does not provide an accurate indication of temperature even at the skin surface.
3o these readings varying with such factors as skin layer thickness, skin roughness and skin color in addition to temperature. Infrared sensors also provide virtually no information as to skin temperature at a depth below the surface. Therefore, such detection has heretofore been used only for gross controls, for example to turn off the laser if an emergency temperature threshold is exceeded or the like, but not to fine tune energy application andlor cooling so as to maintain a desired temperature at a selected depth, for example at the DE junction, thereby facilitating a desired treatment without epidermal damage.
A need therefore exists for an improved technique which permits more accurate determinations of skin temperature at various depths, including at the DE
junction, so as to permit more accurate and more automatic control of EM radiation treatments for various dermatological conditions. In particular, because of variations in skin pigmentation, differences in epidermal depth, and other dermatological differences among patients, laser dermatology procedures are 1 o now performed almost exclusively by physicians or other highly trained individuals, and such individuals must exercise great care to assure that epidermal damage does not occur, while still achieving the desired therapeutic effect. More accurate measurement of temperature at desired depths would make treatments by such skilled personnel easier to perform and would permit such procedures to be safely performed by less highly trained, and therefore less expensive, personnel.
Such skin temperature measurements could also be utilized to determine skin type/pigmentation for the patient and/or for the part of a patient's body being treated and/or for other purposes.
Where cooling of the epidermis is achieved by placing a cooled applicator or other cooled body in contact with the patient's skin, the contact must be made with sufficient pressure to assure good thermal contact between the cooled body and the skin. However, differences in skin thickness and elasticity, differences in bone backing and other factors affect the pressure required to achieve good thermal contact for different patients and for different areas on the body for the same patient. This is another reason why highly trained and skilled individuals are required for performing the treatments and contributes to the high cost of the treatment.
It would therefore be preferable if an automatic technique could be provided for detecting, and thus assuring, good thermal contact between a cooling element and the patient's skin. Such a technique or mechanism, by assuring good thermal contact with the skin before the radiation source is fired, could solve two critical safety problems for radiation dermatology. First, it assures adequate cooling of the epidermis before heating thereof through energy absorption; and second, it assures that the radiation will not be accidentally applied to the eyes or other unwanted place.
3o Related but opposite problems arise in performing certain skin resurfacing/wrinkle removal procedures where the objective is to heat and destroy only the most surface layer of the skin, for example the epidermis, with miumal damage to underlying layers. This requires tight control of factors such as laser energy, pulse duration and repetition rate.
However, variations in patient's skin make such tight control difficult even for highly trained and skilled personnel.
Similar problems also arise in other dermatological procedures involving lasers or other radiation sources.
Another related problem in using an EM radiation source for dermatological treatment is that the skin reflects back a significant portion of the radiation applied thereto. Since this reflected energy does not reach the treatment site, a higher energy radiation source is required to achieve the desired dermatological treatment than would be the case if a larger percentage of the applied radiation reached the treatment site. It lias previously been suggested that one solution I o to this problem is to provide a retro-reflector which collects and returns such back-scattered radiation to the patient's skin. However, existing retro-reflector devices have not optimized the collection and return of such back-scattered radiation and improved techniques for the more efficient reutilization of back-scattered radiation is therefore desirable.
One particular problem with prior art retroreflectors is that they reflect all back-scattered radiation at substantially the same angle the radiation was received; however, radiation at an angle more parallel than perpendicular to the skin surface generally does not reach the treatment area and therefore only heats the surface of the skin, contributing to thermal damage of the skin, without having any beneficial/therapeutic effect. A retroreflection technique which does not contribute to or increase this "parallel" radiation would therefore be desirable.
2o Two other factors can contribute to the efficiency of dermatologic treatments. The first factor is "spot size" or in other words the optical aperture of the applied radiation. Spot size is typically limited by the optics of the handpiece utilized and by the desired fluence as a function of the available energy source. However, a larger spot size permits treatment of large body areas such as back or legs to be accomplished much more quickly, something which enhances both patient satisfaction and practitioner profitability. A technique for facilitating larger spot sizes is thus desirable.
Secondly, anything which reduces the distance from the irradiation source to the target area reduces the amount of energy required to achieve a desired therapeutic effect and anything which permits more of the applied energy to reach the target area has a similar effect. Techniques 3o which facilitate the achievements of these objectives are therefore also desirable.
Summar~r of the Inve tion In accordance with the above, this invention provides both a system for treating a selected dermatologic problem and a head for use in such system. The head, for preferred embodiments includes an optical waveguide or other light path for directing EM radiation of a wavelength appropriate for treating the selected patient dermatologic problem to a first end of the waveguide, the waveguide also having a skin-contacting second end which is opposite the first end; and a sensor at the second end of the waveguide, or otherwise closely adjacent a skin-contacting surface of the head, which senses the temperature thereat. For preferred embodiments, the head also includes a mechanism for removing heat from the waveguide. In order to achieve commercially useful sensitivity, it is preferable that the sensor be located no more than a few millimeters from the skin-contacting surface of the head, for example, the second end of the waveguide, the end contacting the patient's skin. Therefore, for preferred embodiments, the sensor is located within 5 mm of the second end of the waveguide, and for the most preferred embodiments the sensor is located within 1 mm of the second end.
Where a mechanism for removing heat is provided, such mechanism preferably includes a thermoelectric device having one side in thermal contact with the waveguide and an apposite side in thermal contact with a temperature sink. For a preferred embodiment of the invention, back-scattered radiation is substantially internally reflected within the optical waveguide, and there is a reflector within the waveguide for returning back-scattered radiation through the 2o waveguide to the patient's skin. While the reflector may be at a variety of locations within the waveguide, for a preferred embodiment, it is located at the first end of the waveguide. The reflector may also be along sides of the waveguide and the coefficient of reflection for areas of the reflector, either at the f rst end, the side walls or both, may be selected such that back scattered radiation which, before entering the waveguide, at angles nearer perpendicular to the patient's skin are reflected more strongly than backscattered radiation which, before entering the waveguide, are at angles more nearly parallel to the skin surface. The second end of the waveguide in contact with the patient's skin may also have an aperture which is at least substantially as great as the aperture of radiation back-scattered from the patient's skin or a "reflection aperture" substantially as great as the radiation back-scatter aperture may be achieved 3o in other ways. For example, a reflector plate of size to provide the desired reflection aperture may surround the second end of the waveguide. More generally, the invention may include at least one waveguide passing through the head and terminating at a skin-contacting surface -G-thereof, EM radiation being applied through the at least waveguide path to the patient's skin; and a reflection means for returning back-scattered radiation to the patient's skin, which reflection means has a reflection aperture at least substantially as great as the radiation back-scatter aperture. Reflection means may include at least a portion of the skin-contacting surface of the head, which portion may be in the form of a reflection plate, and may also include at least one reflection surface for back-scattered radiation entering the waveguide, at least part of which surface may be in the waveguide.
The system may be for treating a selected dermatological problem in a selected volume of a patient's skin at a depth d which is below the DE junction. A source of EM radiation of a 1 o wavelength appropriate for treating the problem is provided along with an optical waveguide. a mechanism which cools the patient's skin, at least in the portion thereof in contact with the waveguide when the second end of the waveguide is in contact with the patient's skin, and a temperature sensor at the second end of the waveguide. The temperature at the sensor is indicative of the temperature at the patient's DE junction. Finally, controls are provided which are operative in response to the sensor indicating that the DE junction has been cooled to at least a selected temperature for permitting radiation from the source to be passed through the waveguide to the patient's skin. The cooling mechanism preferably removes heat from the waveguide; when in contact with the patient's skin, the waveguide removing heat from and thus cooling the skin. The controls may also be operative in response to the sensor for maintaining 2o the DE junction within a selected temperature range during application of radiation to the patient's skin. The controls may also detect a selected temperature/time profile at the sensor, the profile being indicative of contact of the waveguide with the patient's skin, and may prevent radiation from passing to the patient's skin unless the predetermined profile is detected. This assures that radiation is not applied to the patient's skin unless there is good thermal contact between the radiation-applying waveguide of the head and the patient's skin.
For preferred embodiments, the controls operate the cooling mechanism to cool the waveguide to a desired temperature, the controls being responsive to the sensor for determining when the desired temperature has been reached.
The controls may also be operative in response to the sensor sensing a selected increasing 3o temperature profile at the sensor when the waveguide is placed in contact with the patient's skin for permitting radiation from the source to be passed through the waveguide to the patient's skin.
This control may be instead of the control based on detection that -the DE
junction has been cooled to a selected temperature, but is preferably in addition thereto.
The enhanced retro-reflector features discussed above may also be used in the head independent of the temperature measuring features previously discussed, but are preferably used in conjunction therewith. The invention may also include a head having at least one optical waveguide for receiving EM radiation and for directing it to a skin-contacting surface of the at least one waveguide and a standoff having a first and a second end, with the first end surrounding the at least one waveguide at its lower end and forming a substantially air-tight seal therewith.
The second end of the standoff is adapted to be in contact with the patient's skin over the selected I o volume to form a chamber between the skin-contacting waveguide surface, the patient's skin and walls of the standoff. A means is also provided for creating negative pressure in the chamber to draw the patient's skin therein and into contact with the skin-contact surface. The walls of the standoff are preferable reflective to return back-scattered radiation to the patient's skin. The means for creating negative pressure may include a hose mounted at one end to open into the I 5 chamber and connected at its other end to a source of negative pressure.
Alternatively, the means for creating negative pressure may include the walls of the standoff being deformable when pressure is applied to the head/waveguide to permit the skin-contacting surface of the waveguide to contact the patient's skin, forcing most of the air from the chamber, with the walls of the standoff returning to the their undeformed state when pressure is released, resulting in the 20 creation of negative pressure in the chamber. For example, the walls of the standoff may be in the form of a bellows, suction cup or elastic ring.
Finally, rather than a single optical waveguide, the output surface of a first optical waveguide to which irradiation is initially applied may be mounted to a first surface of a second optical waveguide which also has a second skin-contacting surface opposite the first surface.
25 Optical radiation received from the first waveguide is transmitted through the second waveguide to the skin-contacting surface thereof. The second skin-contacting surface of the second waveguide has a larger area than the output surface of the first waveguide and the second waveguide is formed to provide a larger optical aperture than of the first waveguide. The ratio of the spacing between the first and second surfaces of the second waveguide and a selected 3o surface dimension of the skin-contacting surface of the second waveguide, for example the length of a side of the second surface or a diameter thereof, is approximately 1.5 to 1. Means may be provided for reflecting radiation back-scattered from the patient's skin into the second waveguide _g_ back into the patient's skin. The means for reflecting may include forming at least a portion of the first surface and/or other surfaces of the second waveguide so as to reflect radiation impinging thereon, and such reflection from the second waveguide may also be made angle dependent.
The foregoing and other objects, features and advantages of the invention will be apparent from the following more particular description of preferred embodiments of the invention as illustrated in the accompanying drawings.
In the Drawings_ Fig. 1 is a schematic semi-block diagram of a simplified EM radiation treatment system i o suitable for use in practicing the teachings of this invention.
Fig. 2 is a side sectional view of a head or applicator suitable for use in the system of Fig.
1 in accordance with teachings of this invention.
Fig. 3a is a graph illustrating a calculated relationship over time between the temperature at the waveguide at two Ad's where a sensor may be located and the temperature at three different depths in a patient's skin, including at the DE or basal junction.
Fig. 3b is a graph illustrating a measured relationship over time between the temperature at the waveguide sensor for a preferred Od and the temperature at two different depths in a patient's skin, including at the DE or basal junction.
Fig. 4 is a graph illustrating temperature sensor output over time for selected conditions.
2o Figs. 5a and 5b are simplified side sectional views of two alternative heads or applicators for providing a reflection aperture matching the aperture of radiation back-scatter.
Figs. 6a and 6b are simplified side sectional views of a head or applicator which utilizes negative pressure to draw a fold of skin into a cavity before negative pressure is applied and after negative pressure is applied respectively.
Figs. 7a and 7b are simplified side sectional views of a head or applicator for another embodiment of the invention which utilizes negative pressure to draw a fold of skin into a cavity at an intermediate step in the creation of the negative pressure and after negative pressure has been created respectively.
Figs. 8a, 8b and 8c are simplified side sectional views of a head or applicator for still 3o another embodiment which uses negative pressure to draw a fold of skin into a chamber shown before negative pressure is created, at an intermediate stage in the creation of negative pressure and after negative pressure has been created respectively.
Fig. 9 is a simplified side sectional view of a head for an alternative embodiment of the invention which provides an expanded optical aperture for the head.
Fig. 10 is a simplified side sectional view of a head for an alternative embodiment which head is suitable for moving across a patient's skin during treatment.
Detailed Descri tion Fig. I is a simplified block diagram of a system 10 which may be utilized for treating a selected dermatological condition in accordance with the teachings of this invention. The system includes an electromagnetic (EM) radiation source 12 which is connected through a fiber optic light pipe or other suitable optical conveyor 14 to an applicator or head 16, which head is in contact with the skin 18 of a patient. Controls 20 are provided which receive information from source 12 and head 16 and which control operation of the system in response to these inputs and others. EM source 12 may be a ruby laser, alexandrite laser, diode laser or other laser source providing radiation of a suitable wavelength for the laser treatment to be performed, or may be ~ 5 a lamp or other non-coherent electromagnetic radiation source providing signals at the requisite wavelength. Particularly for non-coherent light sources, various techniques may be utilized to filter, frequency shift or otherwise control the output from the source to achieve radiation within a desired wavelength band. The radiation wavelength may be narrow band, down to a single wavelength, or wide band, and may vary over a wide spectrum from infrared through ultraviolet, 2o depending on the treatment to be performed and the radiation source utilized. Source 12 may be a pulsed source, either under operator control or at a fixed or controlled repetition rate, or may, as taught in copending applications Serial No. 09/078,055, be a continuous wave (CW) source.
Controls 20 may be a suitably programmed general purpose or special purpose computer, may be hard wired circuitry, or may be a hybrid of special purpose circuitry and programmed 25 computer circuitry. Skin 18 has an epidermal layer 22, and a dermal layer 24. the junction of these two layers being sometimes referred to as the DE junction or basal layer 26.
Radiation from source 12 passes through head 16 and is emitted therefrom as a converging beam 28 which is applied to an area 30 in dermis 24 containing the element to be treated. Area 30 may, for example. contain a hair follicle which is to be destroyed in order to 30 achieve removal of unwanted hair, may be tattoo pigment which is to be removed, may be a spider vein or other blood vessel which is to be coagulated and removed or may be some other dermatological condition which is to be treated by the radiation. As discussed earlier, treatment of a patient is complicated by the fact that there may be significant variations among patients, and in different areas of the body of the same patient, in the thickness of epidermal layer 22, in the pigmentation of this layer {and in particular in the quantity of melanin at DE
junction 26), and in other characteristics of the skin. These variations make it difficult to achieve a desired therapeutic effect without potential damage to the area of the patient's epidermis overlyin~1 treatment area 30.
Fig. 2 illustrates a head 16 suitable for use in the system of Fig. 1.
Refernng to Fig. 2, head 16 includes a waveguide or lens 40 of an optically transparent material which also has good heat transfer properties and preferably provides a good index of refraction match with skin.
o Sapphire is a currently preferred material for the waveguide, although other materials could also be used. Waveguide 40 is supported by a holder ring 42 mounted in an exterior housing 44. A
thermocouple, thermistor or other suitable temperature sensor 46 is mounted in contact with waveguide 40, between the waveguide and holder 42. The distance (0d) of sensor 46 from the end of waveguide 40 in contact with the patient's skin is critical and, for reasons to be discussed ~5 later, should be no more than 5 mm. ~d is preferably in the 1-2 mm range, with approximately 1 mm being the currently preferred distance. While a single temperature sensor 46 is shown in Fig. 2, two or more such sensors spaced around waveguide 40 at the same distance Od from the end of the waveguide may be preferable to average out temperature variations which may occur in the waveguide.
2o Thermoelectric cooling elements 48 are also provided in contact with waveguide 40.
While two such elements are shown in Fig. 2, typically at least four such elements, substantially evenly spaced around the periphery of waveguide 40, would normally be provided.
Thermoelectric elements 48 may for example be Peltier elements. Electrical connections are made to sensors) 46 and to thermoelectric elements 48 in a manner known in the art and to 25 simplify the figure are not specifically shown therein.
The sides of thermoelectric elements 48 opposite those in contact with waveguide 40 are in thermal contact with heat sink or radiator 50 having channels 52 formed therein through which a cooling fluid such as air or water flows, the cooling fluid entering the head through a fluid junction 54 and exiting through a fluid junction 56 (or entering though fluid junction 56 and 3o exiting through fluid junction 54).
Optical radiation is applied to the head through an optical fiber, fiber bundle or other light pipe 58 which terminates at a chamber 60. Radiation exiting optical fiber 58 expands in chamber 60 before entering waveguide 40 for application to the patient's skin.- Fiber 58 is mounted in a sleeve 62 of optically opaque material, the rear portion of which is mounted in a tube 64 and the forward portion of which extends through a holder assembly 66. Tube 64 is mounted in a chamber 68 formed in the rear of holder assembly 66 to permit assembly 69, which includes fiber 58, sleeve 62 and tube 64, to be moved forward and backward, moving fiber 58 in chamber 60 to adjust the optical aperture of the head. O-rings 70 and 72 seal chamber 60 to keep air and moisture out so as to avoid condensation on cooled optical surfaces 74 and 76.
Nitrogen or another gas which does not condense at temperatures down to -40°C is utilized to fill chamber 60.
I o Surface 74 of the waveguide is a~~ optical reflecting surface as are all surfaces of chamber 60, including surface 76 at the rear thereof. As will be discussed later, these surfaces retroreflect back-scattered light from the patient's skin. The side walls of both waveguide 40 and chamber 60 may also be fully reflective or may selectively reflect in a manner and for reasons to be discussed later.
In operation, assembly 69 is initially positioned to achieve a desired optical aperture for head 16. Thermoelectric elements 48 are also energized to cool waveguide 40 to a selected temperature, for example 10°C to -40°C. The criteria is to bring the waveguide 40 to a sufficiently low temperature to achieve the desired cooling of epidermis 22 without resulting in tissue temperature being brought down to a level where water in the cells might freeze. Good results have been achieved with a waveguide temperature in the 0°C to -30°C range, with a preferred temperature of approximately -10°C.
When the above preliminary steps have been completed, head 16 may be brought into physical contact with an area of the patient's skin where treatment is to be performed. This contact may be under low pressure, preferably at least sufficient to establish good thermal contact between waveguide 40 and the patient's skin, where the objective is to coagulate blood in for example a spider vein, leg vein or other vein or blood vessel, or may be under pressure greater than the patient's blood pressure for hair removal or other applications where it is preferable to remove blood from the region of skin between waveguide 40 and area 30 under treatment.
In any event, head 16, and in particular waveguide 40 thereof, should be placed in contact 3o with the patient's skin with sufficient pressure to assure good thermal contact between the patient's skin and waveguide 40. In accordance with the teachings of this invention, the fact that such good thermal contact has been established can be detected through use of sensor 46. In particular, as seen in Figs. 3a and 3b, with the sensor positioned approximately I mm fiom the contact surface of waveguide 40, (i.e. Od= 1 mm), the temperature at the sensor has a profile 90 in Fig. 3a and 90' in Fig. 3b which increases sharply for the first quarter to one-half second after such thermal contact has been established. The reason for this is that the waveguide is acting as a heat sink for the patient's skin during this time interval and the heating of the waveguide at the skin-contacting end thereof is greater than the cooling effect of thermoelectric device 48 at this surface (i.e. there is a small temperature gradient across waveguide 40). The detection of the temperature profile 90, 90' by sensors) 46 can be interpreted by controls 20 as an indication of good thermal contact between the waveguide and the patient's skin. If such a thermal profile is ~o not detected, controls 20 inhibit the activation of radiation source 12 and/or prevent radiation from the source being applied to head 16. This assures that radiation is not delivered to the skin unless the epidermis has been adequately cooled to prevent thermal damage thereto.
Referring for example to Fig. 3a, it is seen that the placement of sensor 46 relative to the skin-contacting surface of waveguide 40, or in other words the distance 0d, is critical in order ~5 to achieve this objective. In particular, while profile 90 is achieved for a Od of approximately 1.2 mm, profile 91. which is achieved with a 0d of approximately 4.8 mm, evidences far less sensitivity to temperature changes at the DE junction and is therefore not particularly useful in assuring good thermal contact between the waveguide and the patient's skin.
Actual profile 90' (Fig. 3b), while slightly more stepped and less smooth than the theoretical profile 90 of Fig. 3a, 20 is sufficiently similar to this profile so as to permit easy identification of good thermal contact.
Differences between Figs. 3a and 3b may also arise from the fact that the waveguide in Fig. 3a starts at a temperature of -10°C while the waveguide in Fig. 3b starts at a temperature of approximately -27°C.
Referring again to the Figures, and in particular to Fig. 3a, it is seen that a major portion 25 of the waveguide cooling occurs within a period of between 0.5 and 2 seconds from full contact, the time varying somewhat with the initial temperature of the waveguide and the desired final temperature at the DE junction. Therefore, assuming good thermal contact has been made, an operator may operate source 12 some predetermined time after making contact with the patient's skin, for example a half second thereafter, but not more than approximately 2 seconds thereafter, 3o to avoid significant cooling of the dermis.
However, since cooling of the skin may vary depending on a number of factors, including variations in the equipment being utilized, the color and nature of the patient's skin, the thickness of the patient's skin and the like, it is preferable that the temperature at the DE junction be measured and that the radiation source 12 be operated as soon as this temperature has dropped to a desired level. As can be seen from Figs. 3a and 3b, the temperature profile 90 at sensor 46 tracks the temperature profile 92 at the DE junction as does the temperature profile 90' for DE
junction temperature profile 92'. Thus, the output from sensor 46 can be utilized by control 2U
as an indication of temperature at the DE junction, and radiation source 12 can be operated by control 20 when this temperature reaches a predetermined value. This assures that radiation is not applied to the patient until the patient's epidermis has been fully cooled to the desired level and that the operation of laser source 12 is not delayed so long as to cause cooling of portions of I o the follicle which are to be destroyed. In particular, 94 is a profile taken approximately I mm from the surface of the patient's skin, which is approximately the depth of the bulge in a hair follicle, and may be a depth where other dermatological treatments such as tattoo removal, treatment of port wine stain or vascular legions may occur. From Fig. 3a it is seen that for a time over two seconds, there is a significant drop in temperature at this depth, which can be I 0°C or I5 more. For many dermatological applications, such a drop in temperature I mm into the dermis is undesirable, and in particular can adversely affect the desired treatment.
Curves 96, 96' are temperature profiles with time deeper into the dermis, for example 2 mm therein. At this depth, the cooling effect of cooled waveguide 40 is not significant, perhaps a few degrees Celsius. This lack of cooling effect at deeper depths stems both from the greater distance of these point from 2o the cooling source and from the proximity of tissue at this depth to the warming effect of blood-carrying vessels. The teachings of this invention thus permit and assure that the radiation source is not operated to cause heating of the patient's epidermis until the epidermis has been cooled to the desired depth and temperature, but that firing of the radiation source occurs before there is any significant cooling of the dermis. The invention further permits these controls to be 25 performed completely automatically, thereby reducing the skill level required to safely perform such dermatological procedures, and permitting such procedures to be performed by less skilled and therefore less expensive personnel.
During the firing of the radiation source, control 20 continues to monitor the temperature at sensor 46. If at any time during the firing of the radiation source, there is an increase in 3o temperature at sensor 46 which deviates from what would be anticipated from profile 90, controls 20 can immediately turn off the source 12 to prevent any thermal damage to the patient's epidermis 22.
While for certain treatments, the system of this invention may be able to detect successful completion of the treatment, this is not easy to do, particularly for treatments being performed several millimeters into the dermis. The radiation source is therefore typically fired for a predetermined time interval and/or head 16 is maintained in contact with the patient's skin for a predetermined time interval. Control 20 may determine when such time interval has expired, turn off source I2 when such time period has passed and perhaps generate an audio or visual indication to the operator to remove head 16 from the patient's skin. These steps also reduce the skill level required for using the system.
As indicated earlier, one problem with utilizing radiation to treat dermatological to conditions is that a significant portion of the radiation applied to the patient's skin is back-scattered and lost, therefore increasing the power required from the radiation source utilized, and thus the cost of the system. One solution to this problem is to efficiently collect radiation back-scattered from the patient's skin and to reflect such radiation back into the patient's skin with minimum loss. Fig. 2 shows a retroreflector which is particularly well suited for performing this function. In particular. waveguide 40 has an aperture which is larger than the optical aperture of the radiation applied to the patient's skin and which is instead substantially equal to the aperture of radiation back-scattered from the patient's skin. Thus, substantially all of the back-scattered radiation is collected in waveguide 40. Waveguide 40 has an external coating or is otherwise designed in manners know in the art so as to totally internally reflect the back-scattered radiation collected therein. Some of such radiation impinges on reflecting surface 74 and is returned through the totally internally reflecting waveguide from such surface to the patient's skin. The remainder of the back-scattered radiation extends into chamber 60 which is also totally internally reflected and ultimately impinges on reflecting surface 76 which returns this radiation with minimal loss to the patient's skin. Thus, the retroreflective design for the head 16 in Fig. 2 results in the collection and retroreflection back into the skin of substantially all back-scattered radiation.
In the discussion above, the side walls and back walls of both waveguide 40 and chamber 60 are fully reflecting so that substantially all of the light retroreflected into waveguide 40 is returned to the patient's skin. However, since radiation entering the waveguide from the skin (before refraction on entering the waveguide). is retroreflected back into the patient's skin at 3o substantially the same angle, such radiation at relatively sharp angles, (i.e., at angles more nearly parallel to the patient's skin than perpendicular) contributes primarily to heating the patient's epidermis, potentially causing thermal damage thereto, without reaching region 30, and therefore without having any therapeutic effect. It is therefore preferable that such sharply angled radiation not be retroreflected or that. as a minimum, the retroreflection of such radiation be substantially attenuated. This can be accomplished in the embodiment of Fig. 2 by for example utilizing an angle dependent coating for the side walls of waveguide 40, the rear wall of waveguide 40, or both so that these walls of the waveguide either do not reflect or minimally reflect large angle radiation entering the waveguide, while more strongly reflecting radiation coming in at a more closely perpendicular angle. Alternatively, the side wall may have varying coefficients of reflection, being less reflective for the portions of the wall closest to the tip or skin contacting surface of waveguide 40 and more reflective toward the rear of the waveguide.
Other techniques ~o could also be utilized to assure that waveguide 40 and chamber 60 more strongly reflect retroreflected radiation applied thereto at an angle more nearly perpendicular to the skin surface than radiation applied thereto at an angle more nearly parallel to the skin surface, the perpendicular radiation being substantially fully retroreflected, while the parallel radiation is substantially attenuated.
~ 5 Fig. 4 illustrates the voltage output at sensor 46 as a function of time under selected operating conditions. The solid line 93 illustrates a representative output when the waveguide 40 of head 16 is placed in contact with a patient's skin at time t,. From time t, to time t, the temperature at the sensor increases as the skin in contact with waveguide 40 is cooled. At time tz, source 12 is operating to apply a radiation pulse through the waveguide to the patient's skin 20 causing an increase in the temperature of the patient's skin which is reflected as a spike in the voltage output from the temperature sensor 46. The temperature then decreases rapidly until just before a time tz when backskattered radiation from the patient's skin starts to be received in the waveguide. The time between t~ and t~ is a function of the thickness of the patient's epidermis to the DE junction where melanin is being heated and the amplitude of the spike at time t~ is a 25 function the patient's skin type, more energy being reflected for a patient having darker skin, for example spike 95, than for patients having lighter skin. Thus, the amplitude of the spike which occurs at time t3 may be utilized as an indication of the patient's skin type, and this information may be reviewed at least periodically by the system controls, since skin type will vary even for a given patient as different areas of the patient's skin are being treated.
3o Patient's skin type may also be determined by taking two successive readings, one with head 16 not in contact with the patient's skin and a second with the head in contact with the patient's skin. Curve 93 is an example of the output which is obtained when the head is in contact with the patient's skin, while curve 97 which would start at-time t,.
is indicative of an output which would be obtained when the laser is fired at time t~ with the head not in contact with the patient's skin. Since the output in air is proportional to the coefficient of absorption for air times the applied laser energy (VA=Ic~,E) and VS when the head is in contact with the patient's skin is given by vs - of + oRE
where R is the coefficient of reflection from the patient's skin, R=(V,-V~/k~E). Since k~ and E
are known values, the difference in voltage for the two readings provides a reliable indication of the coefficient of reflection from the patient's skin in the area under treatment. or in other words of the patient's skin type. The output from temperature sensor 46 may also be utilized for other o purposes.
Fig. 5a shows an alternative embodiment of the invention for performing the retroreflector function where the surface area or aperture of waveguide 40 is substantially equal to the optical aperture of radiation applied to the patient's skin. It is therefore smaller than the aperture D of radiation back-scattered from the patient's skin. Therefore, a reflector plate 97 is provided, which ~ 5 may be a specular or diffuse reflector. Plate 97 has a hole which is sized and shaped to permit waveguide 40 to fit therein. Plate 97 may, for example, extend for approximately 1 to 6 millimeters on either side of waveguide 40, but this dimension will vary with application, and can be outside the above range for selected applications. The reflective effect can be enhanced by providing a liquid or other reflective index-matching substance 98 between the skin 18 and 20 the waveguide 40/plate 97, which substance has a reflective index equal or greater than the reflective index of the skin. This decreases the total internal reflection from the skin surface, allowing better return of radiation into the deep layers of skin by reflector 97. Thermoelectric elements 99 in contact with reflective plate 97, which may be formed of a material having good thermal conducting properties such as metal, can be utilized to heat plate 97 to a temperature of, 25 for example, 45-50 C °. Plate 97 can thus preheat the area of the patient's skin surrounding the area where radiation is to be applied, thereby increasing the temperature at the treatment area in the dermis, and thus decreasing the light energy required for performing the desired treatment.
Fig. Sb illustrates an alternative embodiment wherein the reflector 97' has an enhanced efficiency by being formed in a cone or other concave shape. This results in the back-scattered 30 light reflected into the skin being concentrated in the region of the radiation or collimated beam delivered into the skin through waveguide 40, thus increasing the quantity of radiation delivered to the treatment area. Except for the shape of the reflection plate 97', the embodiment of Fig. Sb otherwise functions in the same way as the embodiment of Fig. Sa. As for the embodiment of Fig. 2, retroreflection from waveguide 40 can be angle dependent for the embodiments of Fig.
s Sa and Sb and, particularly for the embodiment of Fig. Sa, reflection from plate 97 can also be made angle dependent by suitably coating the reflecting surface thereof.
Fig. 6a and 6b show another embodiment of the invention which differs from those previously described in that reflection plate 97" is even more angled than for the embodiment of Fig. 5 and is generally in the form of a truncated cone which is secured to the lower end of waveguide 40 in a manner so as to form a substantially air-tight seal therewith. Such securing may be by providing a pressure fit between plate 97" and waveguide 40, but is preferably achieved by applying a suitable adhesive between the two components. Another alternative would be to have some form of screw thread formed in or on waveguide 40 which mates with a corresponding tread on plate 97", but such tread might interfere with the optical properties of 1 s waveguide 40. A hose 100 passes between plate 97" and waveguide 40 and is sealed therebetween, hose l0U being attached to a source of negative pressure (for example vacuum pressure) (not shown). As may be best seen in Fig. 6a, when head 16 of this embodiment is pressed against skin 16, a chamber 99 is formed which is defined by the light reflecting walls of plate 97", the lower surface of waveguide 40, and the surface of the patient's skin 18 which is 20 inside the cone of plate 97". Plate 97" will sometimes also be referred to hereinafter as a standoff.
In operation, once head 16 is in the position shown in Fig. 6a, vacuum is applied through hose 100 to chamber 99 to remove air therefrom. This has the effect of drawing a portion or fold 1 OS of the patient's skin into chamber 99 and into contact with the lower skin-contacting surface of waveguide 40. This can reduce the distance between waveguide 40 and the target volume in 2s skin portion 105 at which treatment is desired and also brings this target volume into chamber 60 where back-scattered radiation retroreflected from the reflecting walls of plate 97" concentrate this radiation on the target volume. This reduces the amount of energy required from EM source 12 and significantly enhances the overall efficiency of the system. The depth of chamber 99 from the bottom of waveguide 40 to the skin surface would typically be in the 5 mm range and should 3o normally not be more than approximately 10 mm. The diameter D of standoff or plate 97" at the skin-contacting end thereof is, as for the embodiment of Figs. Sa and Sb substantially equal to the aperture of back-scatter radiation.
Fig. 7 shows and embodiment of the invention which differs from that shown in Fig. 6 in that, instead of a vacuum line 100 being utilized to obtain reduced or vacuum pressure in chamber 99, standoff 101 is in the form of a bellows which collapses when head 16 is pressed against the skin as shown in Fig. 7a forcing air out of chamber 99. When pressure on head 16 is removed, or if slight upward pressure is applied to the head, bellows 101 straightens as shown in Fig. 7b. The vacuum in chamber 99 holds bellows I O1 against the skin resulting in skin fold 105 again being drawn into chamber 99 as bellows 101 returns to its normal position. The embodiment of Fig. 7 functions substantially the same as the embodiment of Fig. 6 with the inside of bellows 101 having a reflective coating or otherwise being reflective. While the base of bellows or standoff 1 O l has only a slightly larger aperture than the aperture d of waveguide 40, this is not a problem since substantially all of the back-scattered radiation from the skin is emitted into chamber 99 where it is reflected in a concentrated manner back to the target volume and there should be virtually no back-scattered radiation outside of chamber 99. Sharply angled radiation is also productively utilized for these embodiments. An effect substantially the same ~ 5 as that of Fig. 7 can be achieved by using a standoff in the form of a suction cup in lieu of the standoff's 97" or 101 as shown.
Figs. 8a-8c shows still another embodiment of the invention which differs from that shown in Fig. 7 in that a ring 102 of an elastic material is substituted for the bellows 1 O l . When ring 102 is pressed against the skin as shown in Fig. 8b, the ring deforms permitting waveguide 40 to move substantially into contact with skin 18 as air is forced out of chamber 99. When the pressure is released, elastic ring 102 returns to the condition shown in Fig.
8c, resulting in skin fold 105 being drawn into the chamber as shown.
While three standoff configurations have been shown and/or described above for achieving vacuum pressure, or at least negative pressure, in chamber 99 by collapsing a standoff and then permitting it to return to its normal position, the embodiments shown and/or described are by way of illustration only, and other standoff configurations for achieving the same objective might also be utilized. Further, in addition to the use of vacuum hose 100 as shown in Fig. 6, other methods known in the art may be used for achieving the desired reduced pressure in chambers 99 so as to cause a fold of skin 105 to be drawn therein for irradiation.
3o Fig. 9 shows still another embodiment of the invention which differs from those previously shown in that, rather than a bottom surface of waveguide 40 being in contact with the patient's skin 18, the lower end of waveguide 40 is in contact with a second waveguide 103 which RC1'. 1~UN : GF'A-61L_~E_I~1C_ h_iF__!_~~ U3 _ _ _1- _v- 0 : '~'? : 34 fi L7 72U 2_441-_~ _ _ +49 89 2:3994465 : ~ E) 01-05-2000 ~ CA 02323479 2000-o9=ii - - - US 009905501 is prcfaabty of sapphire or other material having good optical and thermal conduction properties.
Sapphire is particularly prefcn'ed, because it also provides a fairly good optical index match with skin. Index matching material 98 may be utilized between waveguide 103 and the patient's skin to further enhance this match. While not specifically shov~n in Fig. 9, waveguide 103 would also have, for prefemcd embodiments, one ar more temperature sensors 46 positioned close to its skin-contacting surface and one or more thermoelectric elements 48 or other temperature control elements in contact therewith to preheat andlor cool the patient's skin t 8 as required. A reflective coating 104 may also be provided on the rear surface of waveguide l 03 to, in conjunction with the retroreflector previously described for wavegttide 40, retroreflect substantially al! radiation back-scattered from the patient's skin. Angle dependent retrorcflection might also be employed for ibis embodiment using techniques previously discussed, such angle dependent retroreffection occurring at least for waveguide 10z, and preferably for both waveguides. 'I~c advantage of the embodiment shown in Fig. 9 is that it significantly enlarges the optical aperiure for treatment, permitting treatment over a relatively large arcs, far example hair removal over a patient's legs or back, to be accomplished far more rapidly then when a head having a smaller apenurc is utilized. T'he skin-contacting surface of waveguide 103 may have a variety of shapes, and may for example be circular or square. A circular waveguide 103 might for example have a diameter of approximately 1 inch (25.4 mm) while a square waveguide 103 might have sides 2 cm long, the height of wavcguide 103 preferable being roughly L5 times this dimension_ These dimensions axe, however, being provided by way of illustration only and the specific dimensions of waveguide 103 will vary with applieat3on.
. In the discussion to this point, it has been assumed tho~t the head utilized is applied to a point on a patient's skin where treattncnt is to be performed and that, after a suitable period of time has passed for cooliag of the skin to the DE junction to have occurred, an optical radiation pulse, far example a Laser pulse, is applied thmugh the waveyuide to treatment area 30. Fig. 10 shows an embodiment of the invention which, like the embodiments taught in application Serial No. 091078,455, is intended to be in contact with die patient's skin 18 and to be moved in direction 112 over the skin while remaining in contact therewith. Radiation applied to waveguides light paths 114 in this head may be continuous wave or may be pulsed at a high enough rate to permit movement of the head over the trr..atment area. For the embodiment shown in Fig. 10, the head has an arcs i t 6 ahead of. waveguides 114 which passes over the treatment area before radiation is applied thereto. Region 116 is preferably of a thermally conductive AMENDED SHEET
material and is insulated from a second region 118 of the head, which is preferably also of a thermally conductive material, by a thermally insulating layer 120. A thermal electric element or other suitable heater/ehiller 122 is in contact with portion 116 and may be used to either preheat or precool the treatment area. For example, if element 122 is a heater, it can heat the skin down to region 30 to a temperature below that at which thermal damage would occur. Further, a temperature sensor 124 is provided, for example up to 5 mm from the skin contacting surface (and preferably less, i.e., to 1 to 2 mm) to indicate skin temperature at for example the DE
junction. Sensor 124, by detecting the heating of melanin in the epidermis provides an indication of skin type for the patient, which indication can be used to control the radiation applied. It also i o assures that overheating in the epidermis does not occur. A thermal electric element or other suitable cooler 126 connected to region 118 cools the epidermis ahead of waveguides 114 coming over a treatment area. A temperature sensor 128 can also be provided in region 118, for example up to 5 mm from the skin contacting surface, to assure that this region has cooled sufficiently before radiation is applied thereto and to protect against thermal damage to this region. While ! 5 a single pair of waveguides 114 are shown in Fig. 10, typically a plurality of such waveguides would be stacked adjacent to each other in a direction into the figure. Two or more heaters/chillers 122, 126 could also be provided and two or more sensors 124, 128 could also be provided. Further, the sensor technology of this invention could also be utilized with other ones of the embodiments shown in application Serial No. 09/078,055.
2o While the invention has been described above with reference to a particular system 10 and to particular head designs 16, neither are limitations on the invention. In particular, other techniques known in the art, for example circulating water or air, could be utilized for cooling waveguide 40 in lieu of thermoelectronic cooling elements 48, although such thennoelectronic cooling elements are at this time preferred. Some elements 48 (or other thermal control elements) 25 might also be used to heat waveguide 40 to preheat the target area, after which either the same or different thermal control elements would be used to cool the waveguide as previously indicated to cool the patient's epidermis in the treatment area. A lens may also be substituted for waveguide 40. although waveguide 40 is currently preferred because of its superior thermal properties and its superior performance in retroreflection. Other light guiding/transmitting 3o element may also be used and, in some applications, two or more such elements may be used as shown in Fig. 10, rather than a single element to transmit EM radiation through the head to the patient's skin. Other details of construction for head 16 or head 110 may also be varied, depending on application. Thus, while the invention has been particularly shown and described above with reference to preferred embodiments, the foregoing and other changes in form and detail may be made therein by one skilled in the ant while still remaining within spirit and scope of the invention which is to be defined only by the appended claims.
Where a mechanism for removing heat is provided, such mechanism preferably includes a thermoelectric device having one side in thermal contact with the waveguide and an apposite side in thermal contact with a temperature sink. For a preferred embodiment of the invention, back-scattered radiation is substantially internally reflected within the optical waveguide, and there is a reflector within the waveguide for returning back-scattered radiation through the 2o waveguide to the patient's skin. While the reflector may be at a variety of locations within the waveguide, for a preferred embodiment, it is located at the first end of the waveguide. The reflector may also be along sides of the waveguide and the coefficient of reflection for areas of the reflector, either at the f rst end, the side walls or both, may be selected such that back scattered radiation which, before entering the waveguide, at angles nearer perpendicular to the patient's skin are reflected more strongly than backscattered radiation which, before entering the waveguide, are at angles more nearly parallel to the skin surface. The second end of the waveguide in contact with the patient's skin may also have an aperture which is at least substantially as great as the aperture of radiation back-scattered from the patient's skin or a "reflection aperture" substantially as great as the radiation back-scatter aperture may be achieved 3o in other ways. For example, a reflector plate of size to provide the desired reflection aperture may surround the second end of the waveguide. More generally, the invention may include at least one waveguide passing through the head and terminating at a skin-contacting surface -G-thereof, EM radiation being applied through the at least waveguide path to the patient's skin; and a reflection means for returning back-scattered radiation to the patient's skin, which reflection means has a reflection aperture at least substantially as great as the radiation back-scatter aperture. Reflection means may include at least a portion of the skin-contacting surface of the head, which portion may be in the form of a reflection plate, and may also include at least one reflection surface for back-scattered radiation entering the waveguide, at least part of which surface may be in the waveguide.
The system may be for treating a selected dermatological problem in a selected volume of a patient's skin at a depth d which is below the DE junction. A source of EM radiation of a 1 o wavelength appropriate for treating the problem is provided along with an optical waveguide. a mechanism which cools the patient's skin, at least in the portion thereof in contact with the waveguide when the second end of the waveguide is in contact with the patient's skin, and a temperature sensor at the second end of the waveguide. The temperature at the sensor is indicative of the temperature at the patient's DE junction. Finally, controls are provided which are operative in response to the sensor indicating that the DE junction has been cooled to at least a selected temperature for permitting radiation from the source to be passed through the waveguide to the patient's skin. The cooling mechanism preferably removes heat from the waveguide; when in contact with the patient's skin, the waveguide removing heat from and thus cooling the skin. The controls may also be operative in response to the sensor for maintaining 2o the DE junction within a selected temperature range during application of radiation to the patient's skin. The controls may also detect a selected temperature/time profile at the sensor, the profile being indicative of contact of the waveguide with the patient's skin, and may prevent radiation from passing to the patient's skin unless the predetermined profile is detected. This assures that radiation is not applied to the patient's skin unless there is good thermal contact between the radiation-applying waveguide of the head and the patient's skin.
For preferred embodiments, the controls operate the cooling mechanism to cool the waveguide to a desired temperature, the controls being responsive to the sensor for determining when the desired temperature has been reached.
The controls may also be operative in response to the sensor sensing a selected increasing 3o temperature profile at the sensor when the waveguide is placed in contact with the patient's skin for permitting radiation from the source to be passed through the waveguide to the patient's skin.
This control may be instead of the control based on detection that -the DE
junction has been cooled to a selected temperature, but is preferably in addition thereto.
The enhanced retro-reflector features discussed above may also be used in the head independent of the temperature measuring features previously discussed, but are preferably used in conjunction therewith. The invention may also include a head having at least one optical waveguide for receiving EM radiation and for directing it to a skin-contacting surface of the at least one waveguide and a standoff having a first and a second end, with the first end surrounding the at least one waveguide at its lower end and forming a substantially air-tight seal therewith.
The second end of the standoff is adapted to be in contact with the patient's skin over the selected I o volume to form a chamber between the skin-contacting waveguide surface, the patient's skin and walls of the standoff. A means is also provided for creating negative pressure in the chamber to draw the patient's skin therein and into contact with the skin-contact surface. The walls of the standoff are preferable reflective to return back-scattered radiation to the patient's skin. The means for creating negative pressure may include a hose mounted at one end to open into the I 5 chamber and connected at its other end to a source of negative pressure.
Alternatively, the means for creating negative pressure may include the walls of the standoff being deformable when pressure is applied to the head/waveguide to permit the skin-contacting surface of the waveguide to contact the patient's skin, forcing most of the air from the chamber, with the walls of the standoff returning to the their undeformed state when pressure is released, resulting in the 20 creation of negative pressure in the chamber. For example, the walls of the standoff may be in the form of a bellows, suction cup or elastic ring.
Finally, rather than a single optical waveguide, the output surface of a first optical waveguide to which irradiation is initially applied may be mounted to a first surface of a second optical waveguide which also has a second skin-contacting surface opposite the first surface.
25 Optical radiation received from the first waveguide is transmitted through the second waveguide to the skin-contacting surface thereof. The second skin-contacting surface of the second waveguide has a larger area than the output surface of the first waveguide and the second waveguide is formed to provide a larger optical aperture than of the first waveguide. The ratio of the spacing between the first and second surfaces of the second waveguide and a selected 3o surface dimension of the skin-contacting surface of the second waveguide, for example the length of a side of the second surface or a diameter thereof, is approximately 1.5 to 1. Means may be provided for reflecting radiation back-scattered from the patient's skin into the second waveguide _g_ back into the patient's skin. The means for reflecting may include forming at least a portion of the first surface and/or other surfaces of the second waveguide so as to reflect radiation impinging thereon, and such reflection from the second waveguide may also be made angle dependent.
The foregoing and other objects, features and advantages of the invention will be apparent from the following more particular description of preferred embodiments of the invention as illustrated in the accompanying drawings.
In the Drawings_ Fig. 1 is a schematic semi-block diagram of a simplified EM radiation treatment system i o suitable for use in practicing the teachings of this invention.
Fig. 2 is a side sectional view of a head or applicator suitable for use in the system of Fig.
1 in accordance with teachings of this invention.
Fig. 3a is a graph illustrating a calculated relationship over time between the temperature at the waveguide at two Ad's where a sensor may be located and the temperature at three different depths in a patient's skin, including at the DE or basal junction.
Fig. 3b is a graph illustrating a measured relationship over time between the temperature at the waveguide sensor for a preferred Od and the temperature at two different depths in a patient's skin, including at the DE or basal junction.
Fig. 4 is a graph illustrating temperature sensor output over time for selected conditions.
2o Figs. 5a and 5b are simplified side sectional views of two alternative heads or applicators for providing a reflection aperture matching the aperture of radiation back-scatter.
Figs. 6a and 6b are simplified side sectional views of a head or applicator which utilizes negative pressure to draw a fold of skin into a cavity before negative pressure is applied and after negative pressure is applied respectively.
Figs. 7a and 7b are simplified side sectional views of a head or applicator for another embodiment of the invention which utilizes negative pressure to draw a fold of skin into a cavity at an intermediate step in the creation of the negative pressure and after negative pressure has been created respectively.
Figs. 8a, 8b and 8c are simplified side sectional views of a head or applicator for still 3o another embodiment which uses negative pressure to draw a fold of skin into a chamber shown before negative pressure is created, at an intermediate stage in the creation of negative pressure and after negative pressure has been created respectively.
Fig. 9 is a simplified side sectional view of a head for an alternative embodiment of the invention which provides an expanded optical aperture for the head.
Fig. 10 is a simplified side sectional view of a head for an alternative embodiment which head is suitable for moving across a patient's skin during treatment.
Detailed Descri tion Fig. I is a simplified block diagram of a system 10 which may be utilized for treating a selected dermatological condition in accordance with the teachings of this invention. The system includes an electromagnetic (EM) radiation source 12 which is connected through a fiber optic light pipe or other suitable optical conveyor 14 to an applicator or head 16, which head is in contact with the skin 18 of a patient. Controls 20 are provided which receive information from source 12 and head 16 and which control operation of the system in response to these inputs and others. EM source 12 may be a ruby laser, alexandrite laser, diode laser or other laser source providing radiation of a suitable wavelength for the laser treatment to be performed, or may be ~ 5 a lamp or other non-coherent electromagnetic radiation source providing signals at the requisite wavelength. Particularly for non-coherent light sources, various techniques may be utilized to filter, frequency shift or otherwise control the output from the source to achieve radiation within a desired wavelength band. The radiation wavelength may be narrow band, down to a single wavelength, or wide band, and may vary over a wide spectrum from infrared through ultraviolet, 2o depending on the treatment to be performed and the radiation source utilized. Source 12 may be a pulsed source, either under operator control or at a fixed or controlled repetition rate, or may, as taught in copending applications Serial No. 09/078,055, be a continuous wave (CW) source.
Controls 20 may be a suitably programmed general purpose or special purpose computer, may be hard wired circuitry, or may be a hybrid of special purpose circuitry and programmed 25 computer circuitry. Skin 18 has an epidermal layer 22, and a dermal layer 24. the junction of these two layers being sometimes referred to as the DE junction or basal layer 26.
Radiation from source 12 passes through head 16 and is emitted therefrom as a converging beam 28 which is applied to an area 30 in dermis 24 containing the element to be treated. Area 30 may, for example. contain a hair follicle which is to be destroyed in order to 30 achieve removal of unwanted hair, may be tattoo pigment which is to be removed, may be a spider vein or other blood vessel which is to be coagulated and removed or may be some other dermatological condition which is to be treated by the radiation. As discussed earlier, treatment of a patient is complicated by the fact that there may be significant variations among patients, and in different areas of the body of the same patient, in the thickness of epidermal layer 22, in the pigmentation of this layer {and in particular in the quantity of melanin at DE
junction 26), and in other characteristics of the skin. These variations make it difficult to achieve a desired therapeutic effect without potential damage to the area of the patient's epidermis overlyin~1 treatment area 30.
Fig. 2 illustrates a head 16 suitable for use in the system of Fig. 1.
Refernng to Fig. 2, head 16 includes a waveguide or lens 40 of an optically transparent material which also has good heat transfer properties and preferably provides a good index of refraction match with skin.
o Sapphire is a currently preferred material for the waveguide, although other materials could also be used. Waveguide 40 is supported by a holder ring 42 mounted in an exterior housing 44. A
thermocouple, thermistor or other suitable temperature sensor 46 is mounted in contact with waveguide 40, between the waveguide and holder 42. The distance (0d) of sensor 46 from the end of waveguide 40 in contact with the patient's skin is critical and, for reasons to be discussed ~5 later, should be no more than 5 mm. ~d is preferably in the 1-2 mm range, with approximately 1 mm being the currently preferred distance. While a single temperature sensor 46 is shown in Fig. 2, two or more such sensors spaced around waveguide 40 at the same distance Od from the end of the waveguide may be preferable to average out temperature variations which may occur in the waveguide.
2o Thermoelectric cooling elements 48 are also provided in contact with waveguide 40.
While two such elements are shown in Fig. 2, typically at least four such elements, substantially evenly spaced around the periphery of waveguide 40, would normally be provided.
Thermoelectric elements 48 may for example be Peltier elements. Electrical connections are made to sensors) 46 and to thermoelectric elements 48 in a manner known in the art and to 25 simplify the figure are not specifically shown therein.
The sides of thermoelectric elements 48 opposite those in contact with waveguide 40 are in thermal contact with heat sink or radiator 50 having channels 52 formed therein through which a cooling fluid such as air or water flows, the cooling fluid entering the head through a fluid junction 54 and exiting through a fluid junction 56 (or entering though fluid junction 56 and 3o exiting through fluid junction 54).
Optical radiation is applied to the head through an optical fiber, fiber bundle or other light pipe 58 which terminates at a chamber 60. Radiation exiting optical fiber 58 expands in chamber 60 before entering waveguide 40 for application to the patient's skin.- Fiber 58 is mounted in a sleeve 62 of optically opaque material, the rear portion of which is mounted in a tube 64 and the forward portion of which extends through a holder assembly 66. Tube 64 is mounted in a chamber 68 formed in the rear of holder assembly 66 to permit assembly 69, which includes fiber 58, sleeve 62 and tube 64, to be moved forward and backward, moving fiber 58 in chamber 60 to adjust the optical aperture of the head. O-rings 70 and 72 seal chamber 60 to keep air and moisture out so as to avoid condensation on cooled optical surfaces 74 and 76.
Nitrogen or another gas which does not condense at temperatures down to -40°C is utilized to fill chamber 60.
I o Surface 74 of the waveguide is a~~ optical reflecting surface as are all surfaces of chamber 60, including surface 76 at the rear thereof. As will be discussed later, these surfaces retroreflect back-scattered light from the patient's skin. The side walls of both waveguide 40 and chamber 60 may also be fully reflective or may selectively reflect in a manner and for reasons to be discussed later.
In operation, assembly 69 is initially positioned to achieve a desired optical aperture for head 16. Thermoelectric elements 48 are also energized to cool waveguide 40 to a selected temperature, for example 10°C to -40°C. The criteria is to bring the waveguide 40 to a sufficiently low temperature to achieve the desired cooling of epidermis 22 without resulting in tissue temperature being brought down to a level where water in the cells might freeze. Good results have been achieved with a waveguide temperature in the 0°C to -30°C range, with a preferred temperature of approximately -10°C.
When the above preliminary steps have been completed, head 16 may be brought into physical contact with an area of the patient's skin where treatment is to be performed. This contact may be under low pressure, preferably at least sufficient to establish good thermal contact between waveguide 40 and the patient's skin, where the objective is to coagulate blood in for example a spider vein, leg vein or other vein or blood vessel, or may be under pressure greater than the patient's blood pressure for hair removal or other applications where it is preferable to remove blood from the region of skin between waveguide 40 and area 30 under treatment.
In any event, head 16, and in particular waveguide 40 thereof, should be placed in contact 3o with the patient's skin with sufficient pressure to assure good thermal contact between the patient's skin and waveguide 40. In accordance with the teachings of this invention, the fact that such good thermal contact has been established can be detected through use of sensor 46. In particular, as seen in Figs. 3a and 3b, with the sensor positioned approximately I mm fiom the contact surface of waveguide 40, (i.e. Od= 1 mm), the temperature at the sensor has a profile 90 in Fig. 3a and 90' in Fig. 3b which increases sharply for the first quarter to one-half second after such thermal contact has been established. The reason for this is that the waveguide is acting as a heat sink for the patient's skin during this time interval and the heating of the waveguide at the skin-contacting end thereof is greater than the cooling effect of thermoelectric device 48 at this surface (i.e. there is a small temperature gradient across waveguide 40). The detection of the temperature profile 90, 90' by sensors) 46 can be interpreted by controls 20 as an indication of good thermal contact between the waveguide and the patient's skin. If such a thermal profile is ~o not detected, controls 20 inhibit the activation of radiation source 12 and/or prevent radiation from the source being applied to head 16. This assures that radiation is not delivered to the skin unless the epidermis has been adequately cooled to prevent thermal damage thereto.
Referring for example to Fig. 3a, it is seen that the placement of sensor 46 relative to the skin-contacting surface of waveguide 40, or in other words the distance 0d, is critical in order ~5 to achieve this objective. In particular, while profile 90 is achieved for a Od of approximately 1.2 mm, profile 91. which is achieved with a 0d of approximately 4.8 mm, evidences far less sensitivity to temperature changes at the DE junction and is therefore not particularly useful in assuring good thermal contact between the waveguide and the patient's skin.
Actual profile 90' (Fig. 3b), while slightly more stepped and less smooth than the theoretical profile 90 of Fig. 3a, 20 is sufficiently similar to this profile so as to permit easy identification of good thermal contact.
Differences between Figs. 3a and 3b may also arise from the fact that the waveguide in Fig. 3a starts at a temperature of -10°C while the waveguide in Fig. 3b starts at a temperature of approximately -27°C.
Referring again to the Figures, and in particular to Fig. 3a, it is seen that a major portion 25 of the waveguide cooling occurs within a period of between 0.5 and 2 seconds from full contact, the time varying somewhat with the initial temperature of the waveguide and the desired final temperature at the DE junction. Therefore, assuming good thermal contact has been made, an operator may operate source 12 some predetermined time after making contact with the patient's skin, for example a half second thereafter, but not more than approximately 2 seconds thereafter, 3o to avoid significant cooling of the dermis.
However, since cooling of the skin may vary depending on a number of factors, including variations in the equipment being utilized, the color and nature of the patient's skin, the thickness of the patient's skin and the like, it is preferable that the temperature at the DE junction be measured and that the radiation source 12 be operated as soon as this temperature has dropped to a desired level. As can be seen from Figs. 3a and 3b, the temperature profile 90 at sensor 46 tracks the temperature profile 92 at the DE junction as does the temperature profile 90' for DE
junction temperature profile 92'. Thus, the output from sensor 46 can be utilized by control 2U
as an indication of temperature at the DE junction, and radiation source 12 can be operated by control 20 when this temperature reaches a predetermined value. This assures that radiation is not applied to the patient until the patient's epidermis has been fully cooled to the desired level and that the operation of laser source 12 is not delayed so long as to cause cooling of portions of I o the follicle which are to be destroyed. In particular, 94 is a profile taken approximately I mm from the surface of the patient's skin, which is approximately the depth of the bulge in a hair follicle, and may be a depth where other dermatological treatments such as tattoo removal, treatment of port wine stain or vascular legions may occur. From Fig. 3a it is seen that for a time over two seconds, there is a significant drop in temperature at this depth, which can be I 0°C or I5 more. For many dermatological applications, such a drop in temperature I mm into the dermis is undesirable, and in particular can adversely affect the desired treatment.
Curves 96, 96' are temperature profiles with time deeper into the dermis, for example 2 mm therein. At this depth, the cooling effect of cooled waveguide 40 is not significant, perhaps a few degrees Celsius. This lack of cooling effect at deeper depths stems both from the greater distance of these point from 2o the cooling source and from the proximity of tissue at this depth to the warming effect of blood-carrying vessels. The teachings of this invention thus permit and assure that the radiation source is not operated to cause heating of the patient's epidermis until the epidermis has been cooled to the desired depth and temperature, but that firing of the radiation source occurs before there is any significant cooling of the dermis. The invention further permits these controls to be 25 performed completely automatically, thereby reducing the skill level required to safely perform such dermatological procedures, and permitting such procedures to be performed by less skilled and therefore less expensive personnel.
During the firing of the radiation source, control 20 continues to monitor the temperature at sensor 46. If at any time during the firing of the radiation source, there is an increase in 3o temperature at sensor 46 which deviates from what would be anticipated from profile 90, controls 20 can immediately turn off the source 12 to prevent any thermal damage to the patient's epidermis 22.
While for certain treatments, the system of this invention may be able to detect successful completion of the treatment, this is not easy to do, particularly for treatments being performed several millimeters into the dermis. The radiation source is therefore typically fired for a predetermined time interval and/or head 16 is maintained in contact with the patient's skin for a predetermined time interval. Control 20 may determine when such time interval has expired, turn off source I2 when such time period has passed and perhaps generate an audio or visual indication to the operator to remove head 16 from the patient's skin. These steps also reduce the skill level required for using the system.
As indicated earlier, one problem with utilizing radiation to treat dermatological to conditions is that a significant portion of the radiation applied to the patient's skin is back-scattered and lost, therefore increasing the power required from the radiation source utilized, and thus the cost of the system. One solution to this problem is to efficiently collect radiation back-scattered from the patient's skin and to reflect such radiation back into the patient's skin with minimum loss. Fig. 2 shows a retroreflector which is particularly well suited for performing this function. In particular. waveguide 40 has an aperture which is larger than the optical aperture of the radiation applied to the patient's skin and which is instead substantially equal to the aperture of radiation back-scattered from the patient's skin. Thus, substantially all of the back-scattered radiation is collected in waveguide 40. Waveguide 40 has an external coating or is otherwise designed in manners know in the art so as to totally internally reflect the back-scattered radiation collected therein. Some of such radiation impinges on reflecting surface 74 and is returned through the totally internally reflecting waveguide from such surface to the patient's skin. The remainder of the back-scattered radiation extends into chamber 60 which is also totally internally reflected and ultimately impinges on reflecting surface 76 which returns this radiation with minimal loss to the patient's skin. Thus, the retroreflective design for the head 16 in Fig. 2 results in the collection and retroreflection back into the skin of substantially all back-scattered radiation.
In the discussion above, the side walls and back walls of both waveguide 40 and chamber 60 are fully reflecting so that substantially all of the light retroreflected into waveguide 40 is returned to the patient's skin. However, since radiation entering the waveguide from the skin (before refraction on entering the waveguide). is retroreflected back into the patient's skin at 3o substantially the same angle, such radiation at relatively sharp angles, (i.e., at angles more nearly parallel to the patient's skin than perpendicular) contributes primarily to heating the patient's epidermis, potentially causing thermal damage thereto, without reaching region 30, and therefore without having any therapeutic effect. It is therefore preferable that such sharply angled radiation not be retroreflected or that. as a minimum, the retroreflection of such radiation be substantially attenuated. This can be accomplished in the embodiment of Fig. 2 by for example utilizing an angle dependent coating for the side walls of waveguide 40, the rear wall of waveguide 40, or both so that these walls of the waveguide either do not reflect or minimally reflect large angle radiation entering the waveguide, while more strongly reflecting radiation coming in at a more closely perpendicular angle. Alternatively, the side wall may have varying coefficients of reflection, being less reflective for the portions of the wall closest to the tip or skin contacting surface of waveguide 40 and more reflective toward the rear of the waveguide.
Other techniques ~o could also be utilized to assure that waveguide 40 and chamber 60 more strongly reflect retroreflected radiation applied thereto at an angle more nearly perpendicular to the skin surface than radiation applied thereto at an angle more nearly parallel to the skin surface, the perpendicular radiation being substantially fully retroreflected, while the parallel radiation is substantially attenuated.
~ 5 Fig. 4 illustrates the voltage output at sensor 46 as a function of time under selected operating conditions. The solid line 93 illustrates a representative output when the waveguide 40 of head 16 is placed in contact with a patient's skin at time t,. From time t, to time t, the temperature at the sensor increases as the skin in contact with waveguide 40 is cooled. At time tz, source 12 is operating to apply a radiation pulse through the waveguide to the patient's skin 20 causing an increase in the temperature of the patient's skin which is reflected as a spike in the voltage output from the temperature sensor 46. The temperature then decreases rapidly until just before a time tz when backskattered radiation from the patient's skin starts to be received in the waveguide. The time between t~ and t~ is a function of the thickness of the patient's epidermis to the DE junction where melanin is being heated and the amplitude of the spike at time t~ is a 25 function the patient's skin type, more energy being reflected for a patient having darker skin, for example spike 95, than for patients having lighter skin. Thus, the amplitude of the spike which occurs at time t3 may be utilized as an indication of the patient's skin type, and this information may be reviewed at least periodically by the system controls, since skin type will vary even for a given patient as different areas of the patient's skin are being treated.
3o Patient's skin type may also be determined by taking two successive readings, one with head 16 not in contact with the patient's skin and a second with the head in contact with the patient's skin. Curve 93 is an example of the output which is obtained when the head is in contact with the patient's skin, while curve 97 which would start at-time t,.
is indicative of an output which would be obtained when the laser is fired at time t~ with the head not in contact with the patient's skin. Since the output in air is proportional to the coefficient of absorption for air times the applied laser energy (VA=Ic~,E) and VS when the head is in contact with the patient's skin is given by vs - of + oRE
where R is the coefficient of reflection from the patient's skin, R=(V,-V~/k~E). Since k~ and E
are known values, the difference in voltage for the two readings provides a reliable indication of the coefficient of reflection from the patient's skin in the area under treatment. or in other words of the patient's skin type. The output from temperature sensor 46 may also be utilized for other o purposes.
Fig. 5a shows an alternative embodiment of the invention for performing the retroreflector function where the surface area or aperture of waveguide 40 is substantially equal to the optical aperture of radiation applied to the patient's skin. It is therefore smaller than the aperture D of radiation back-scattered from the patient's skin. Therefore, a reflector plate 97 is provided, which ~ 5 may be a specular or diffuse reflector. Plate 97 has a hole which is sized and shaped to permit waveguide 40 to fit therein. Plate 97 may, for example, extend for approximately 1 to 6 millimeters on either side of waveguide 40, but this dimension will vary with application, and can be outside the above range for selected applications. The reflective effect can be enhanced by providing a liquid or other reflective index-matching substance 98 between the skin 18 and 20 the waveguide 40/plate 97, which substance has a reflective index equal or greater than the reflective index of the skin. This decreases the total internal reflection from the skin surface, allowing better return of radiation into the deep layers of skin by reflector 97. Thermoelectric elements 99 in contact with reflective plate 97, which may be formed of a material having good thermal conducting properties such as metal, can be utilized to heat plate 97 to a temperature of, 25 for example, 45-50 C °. Plate 97 can thus preheat the area of the patient's skin surrounding the area where radiation is to be applied, thereby increasing the temperature at the treatment area in the dermis, and thus decreasing the light energy required for performing the desired treatment.
Fig. Sb illustrates an alternative embodiment wherein the reflector 97' has an enhanced efficiency by being formed in a cone or other concave shape. This results in the back-scattered 30 light reflected into the skin being concentrated in the region of the radiation or collimated beam delivered into the skin through waveguide 40, thus increasing the quantity of radiation delivered to the treatment area. Except for the shape of the reflection plate 97', the embodiment of Fig. Sb otherwise functions in the same way as the embodiment of Fig. Sa. As for the embodiment of Fig. 2, retroreflection from waveguide 40 can be angle dependent for the embodiments of Fig.
s Sa and Sb and, particularly for the embodiment of Fig. Sa, reflection from plate 97 can also be made angle dependent by suitably coating the reflecting surface thereof.
Fig. 6a and 6b show another embodiment of the invention which differs from those previously described in that reflection plate 97" is even more angled than for the embodiment of Fig. 5 and is generally in the form of a truncated cone which is secured to the lower end of waveguide 40 in a manner so as to form a substantially air-tight seal therewith. Such securing may be by providing a pressure fit between plate 97" and waveguide 40, but is preferably achieved by applying a suitable adhesive between the two components. Another alternative would be to have some form of screw thread formed in or on waveguide 40 which mates with a corresponding tread on plate 97", but such tread might interfere with the optical properties of 1 s waveguide 40. A hose 100 passes between plate 97" and waveguide 40 and is sealed therebetween, hose l0U being attached to a source of negative pressure (for example vacuum pressure) (not shown). As may be best seen in Fig. 6a, when head 16 of this embodiment is pressed against skin 16, a chamber 99 is formed which is defined by the light reflecting walls of plate 97", the lower surface of waveguide 40, and the surface of the patient's skin 18 which is 20 inside the cone of plate 97". Plate 97" will sometimes also be referred to hereinafter as a standoff.
In operation, once head 16 is in the position shown in Fig. 6a, vacuum is applied through hose 100 to chamber 99 to remove air therefrom. This has the effect of drawing a portion or fold 1 OS of the patient's skin into chamber 99 and into contact with the lower skin-contacting surface of waveguide 40. This can reduce the distance between waveguide 40 and the target volume in 2s skin portion 105 at which treatment is desired and also brings this target volume into chamber 60 where back-scattered radiation retroreflected from the reflecting walls of plate 97" concentrate this radiation on the target volume. This reduces the amount of energy required from EM source 12 and significantly enhances the overall efficiency of the system. The depth of chamber 99 from the bottom of waveguide 40 to the skin surface would typically be in the 5 mm range and should 3o normally not be more than approximately 10 mm. The diameter D of standoff or plate 97" at the skin-contacting end thereof is, as for the embodiment of Figs. Sa and Sb substantially equal to the aperture of back-scatter radiation.
Fig. 7 shows and embodiment of the invention which differs from that shown in Fig. 6 in that, instead of a vacuum line 100 being utilized to obtain reduced or vacuum pressure in chamber 99, standoff 101 is in the form of a bellows which collapses when head 16 is pressed against the skin as shown in Fig. 7a forcing air out of chamber 99. When pressure on head 16 is removed, or if slight upward pressure is applied to the head, bellows 101 straightens as shown in Fig. 7b. The vacuum in chamber 99 holds bellows I O1 against the skin resulting in skin fold 105 again being drawn into chamber 99 as bellows 101 returns to its normal position. The embodiment of Fig. 7 functions substantially the same as the embodiment of Fig. 6 with the inside of bellows 101 having a reflective coating or otherwise being reflective. While the base of bellows or standoff 1 O l has only a slightly larger aperture than the aperture d of waveguide 40, this is not a problem since substantially all of the back-scattered radiation from the skin is emitted into chamber 99 where it is reflected in a concentrated manner back to the target volume and there should be virtually no back-scattered radiation outside of chamber 99. Sharply angled radiation is also productively utilized for these embodiments. An effect substantially the same ~ 5 as that of Fig. 7 can be achieved by using a standoff in the form of a suction cup in lieu of the standoff's 97" or 101 as shown.
Figs. 8a-8c shows still another embodiment of the invention which differs from that shown in Fig. 7 in that a ring 102 of an elastic material is substituted for the bellows 1 O l . When ring 102 is pressed against the skin as shown in Fig. 8b, the ring deforms permitting waveguide 40 to move substantially into contact with skin 18 as air is forced out of chamber 99. When the pressure is released, elastic ring 102 returns to the condition shown in Fig.
8c, resulting in skin fold 105 being drawn into the chamber as shown.
While three standoff configurations have been shown and/or described above for achieving vacuum pressure, or at least negative pressure, in chamber 99 by collapsing a standoff and then permitting it to return to its normal position, the embodiments shown and/or described are by way of illustration only, and other standoff configurations for achieving the same objective might also be utilized. Further, in addition to the use of vacuum hose 100 as shown in Fig. 6, other methods known in the art may be used for achieving the desired reduced pressure in chambers 99 so as to cause a fold of skin 105 to be drawn therein for irradiation.
3o Fig. 9 shows still another embodiment of the invention which differs from those previously shown in that, rather than a bottom surface of waveguide 40 being in contact with the patient's skin 18, the lower end of waveguide 40 is in contact with a second waveguide 103 which RC1'. 1~UN : GF'A-61L_~E_I~1C_ h_iF__!_~~ U3 _ _ _1- _v- 0 : '~'? : 34 fi L7 72U 2_441-_~ _ _ +49 89 2:3994465 : ~ E) 01-05-2000 ~ CA 02323479 2000-o9=ii - - - US 009905501 is prcfaabty of sapphire or other material having good optical and thermal conduction properties.
Sapphire is particularly prefcn'ed, because it also provides a fairly good optical index match with skin. Index matching material 98 may be utilized between waveguide 103 and the patient's skin to further enhance this match. While not specifically shov~n in Fig. 9, waveguide 103 would also have, for prefemcd embodiments, one ar more temperature sensors 46 positioned close to its skin-contacting surface and one or more thermoelectric elements 48 or other temperature control elements in contact therewith to preheat andlor cool the patient's skin t 8 as required. A reflective coating 104 may also be provided on the rear surface of waveguide l 03 to, in conjunction with the retroreflector previously described for wavegttide 40, retroreflect substantially al! radiation back-scattered from the patient's skin. Angle dependent retrorcflection might also be employed for ibis embodiment using techniques previously discussed, such angle dependent retroreffection occurring at least for waveguide 10z, and preferably for both waveguides. 'I~c advantage of the embodiment shown in Fig. 9 is that it significantly enlarges the optical aperiure for treatment, permitting treatment over a relatively large arcs, far example hair removal over a patient's legs or back, to be accomplished far more rapidly then when a head having a smaller apenurc is utilized. T'he skin-contacting surface of waveguide 103 may have a variety of shapes, and may for example be circular or square. A circular waveguide 103 might for example have a diameter of approximately 1 inch (25.4 mm) while a square waveguide 103 might have sides 2 cm long, the height of wavcguide 103 preferable being roughly L5 times this dimension_ These dimensions axe, however, being provided by way of illustration only and the specific dimensions of waveguide 103 will vary with applieat3on.
. In the discussion to this point, it has been assumed tho~t the head utilized is applied to a point on a patient's skin where treattncnt is to be performed and that, after a suitable period of time has passed for cooliag of the skin to the DE junction to have occurred, an optical radiation pulse, far example a Laser pulse, is applied thmugh the waveyuide to treatment area 30. Fig. 10 shows an embodiment of the invention which, like the embodiments taught in application Serial No. 091078,455, is intended to be in contact with die patient's skin 18 and to be moved in direction 112 over the skin while remaining in contact therewith. Radiation applied to waveguides light paths 114 in this head may be continuous wave or may be pulsed at a high enough rate to permit movement of the head over the trr..atment area. For the embodiment shown in Fig. 10, the head has an arcs i t 6 ahead of. waveguides 114 which passes over the treatment area before radiation is applied thereto. Region 116 is preferably of a thermally conductive AMENDED SHEET
material and is insulated from a second region 118 of the head, which is preferably also of a thermally conductive material, by a thermally insulating layer 120. A thermal electric element or other suitable heater/ehiller 122 is in contact with portion 116 and may be used to either preheat or precool the treatment area. For example, if element 122 is a heater, it can heat the skin down to region 30 to a temperature below that at which thermal damage would occur. Further, a temperature sensor 124 is provided, for example up to 5 mm from the skin contacting surface (and preferably less, i.e., to 1 to 2 mm) to indicate skin temperature at for example the DE
junction. Sensor 124, by detecting the heating of melanin in the epidermis provides an indication of skin type for the patient, which indication can be used to control the radiation applied. It also i o assures that overheating in the epidermis does not occur. A thermal electric element or other suitable cooler 126 connected to region 118 cools the epidermis ahead of waveguides 114 coming over a treatment area. A temperature sensor 128 can also be provided in region 118, for example up to 5 mm from the skin contacting surface, to assure that this region has cooled sufficiently before radiation is applied thereto and to protect against thermal damage to this region. While ! 5 a single pair of waveguides 114 are shown in Fig. 10, typically a plurality of such waveguides would be stacked adjacent to each other in a direction into the figure. Two or more heaters/chillers 122, 126 could also be provided and two or more sensors 124, 128 could also be provided. Further, the sensor technology of this invention could also be utilized with other ones of the embodiments shown in application Serial No. 09/078,055.
2o While the invention has been described above with reference to a particular system 10 and to particular head designs 16, neither are limitations on the invention. In particular, other techniques known in the art, for example circulating water or air, could be utilized for cooling waveguide 40 in lieu of thermoelectronic cooling elements 48, although such thennoelectronic cooling elements are at this time preferred. Some elements 48 (or other thermal control elements) 25 might also be used to heat waveguide 40 to preheat the target area, after which either the same or different thermal control elements would be used to cool the waveguide as previously indicated to cool the patient's epidermis in the treatment area. A lens may also be substituted for waveguide 40. although waveguide 40 is currently preferred because of its superior thermal properties and its superior performance in retroreflection. Other light guiding/transmitting 3o element may also be used and, in some applications, two or more such elements may be used as shown in Fig. 10, rather than a single element to transmit EM radiation through the head to the patient's skin. Other details of construction for head 16 or head 110 may also be varied, depending on application. Thus, while the invention has been particularly shown and described above with reference to preferred embodiments, the foregoing and other changes in form and detail may be made therein by one skilled in the ant while still remaining within spirit and scope of the invention which is to be defined only by the appended claims.
Claims (59)
1. A head 16 for applying EM radiation 28 of a wavelength appropriate for treating a selected patient dermatologic problem to a selected volume 30 of a patient's skin 18, the volume containing the problem to be treated, the head including:
an optical waveguide 40;
a light path 58, etc. for directing the EM radiation to a first end of the waveguide, said waveguide having a skin-contacting second end which is opposite said first end; and a sensor 46 at said second end of the waveguide which senses the temperature thereat.
an optical waveguide 40;
a light path 58, etc. for directing the EM radiation to a first end of the waveguide, said waveguide having a skin-contacting second end which is opposite said first end; and a sensor 46 at said second end of the waveguide which senses the temperature thereat.
2. (cancelled)
3. A head 16 as claimed in claim 1 wherein said sensor 46 is located within less than 5 millimeters of said second end of the waveguide.
4. A head 16 as claimed in claim 2 wherein said sensor 46 is located within 2 millimeters of said second end of the waveguide.
5. A head 16 as claimed in claim 2 wherein said sensor 46 is located within 1 millimeter of said second end of the waveguide.
6. A head 16 as claimed in claim 1 including a mechanism 48, 50, etc. for removing heat from the waveguide 40.
7. A head 16 as claimed in claim 6 wherein said mechanism 48, 50, etc.
includes a thermoelectric device 48 having one side in thermal contact with said waveguide 40 and an opposite side in thermal contact with a temperature sink 50.
includes a thermoelectric device 48 having one side in thermal contact with said waveguide 40 and an opposite side in thermal contact with a temperature sink 50.
8. A head 16 as claimed in claim 1 wherein said head has a reflection aperture D at a skin-contacting end thereof at least substantially as great as the aperture of radiation back-scattered from the patient's skin.
9. A head 16 as claimed in claim 8 wherein said second end of the waveguide has an aperture D at least substantially as great as the aperture of radiation back-scattered from the patient's skin.
10. A head 16 as claimed in claim 8 wherein at least part of the back-scartered radiation enters said waveguide 40 and is substantially internally reflected within said waveguide; and including a reflector 74, etc within said waveguide for returning back-scattered radiation through the waveguide to the patient's skin.
11. A head 16 as claimed in claim 10 wherein said reflector is at said first end of the waveguide.
12. A head 16 as claimed in claim 11 wherein said reflector is also along at least a portion of waveguide sidewalls, and wherein said reflector has a coefficient of reflection at areas thereof such that backscattered radiation at angles nearer perpendicular to said skin contacting second end are reflected more strongly then back scattered radiation at angles nearer parallel to said second end.
13. A head 16 as claimed in claim 8 including a reflector plate 97 surrounding said waveguide 40 at the second end thereof, the combined area of the plate and the waveguide projecting therethrough being substantially equal to the aperture of radiation back-scatter.
14. A head 16 as claimed in claim 13 wherein said plate 97 has a concave shape.
15. A head 16 as claimed in claim 13 including a means 99 for controlling the temperature of the plate.
16. A system for treating a selected dermatologic problem located in a selected volume of a patient's skin at a depth d, which depth is below the DE junction, comprising:
a source of EM radiation of a wavelength appropriate for treating said problem;
an optical waveguide having a first end at which said radiation is applied and a second end for contacting the patient's skin, which second end is opposite said first end;
a temperature sensor at said second end of the waveguide, the temperature at said sensor being indicative of the temperature at a selected depth within the patient's skin; a mechanism which removes heat from the patient's skin at least in the area thereof in contact with said waveguide; and controls operative in response to said sensor indicating that the patient's skin at said selected depth has been cooled to at least a selected temperature for permitting radiation from said source to be passed through said waveguide to the patient's skin, including said selected volume.
a source of EM radiation of a wavelength appropriate for treating said problem;
an optical waveguide having a first end at which said radiation is applied and a second end for contacting the patient's skin, which second end is opposite said first end;
a temperature sensor at said second end of the waveguide, the temperature at said sensor being indicative of the temperature at a selected depth within the patient's skin; a mechanism which removes heat from the patient's skin at least in the area thereof in contact with said waveguide; and controls operative in response to said sensor indicating that the patient's skin at said selected depth has been cooled to at least a selected temperature for permitting radiation from said source to be passed through said waveguide to the patient's skin, including said selected volume.
17. A system as claimed in claim 16 wherein said mechanism removes heat from the waveguide, the waveguide, when in contact with the skin, removing hit from, and thus cooling, the skin.
18. A system as claimed in claim 17 wherein said selected depth is the DE
junction, and wherein said controls are operative in responsive to said sensor for maintaining the DE junction within a selected temperature range during application of said radiation to the patient's skin.
junction, and wherein said controls are operative in responsive to said sensor for maintaining the DE junction within a selected temperature range during application of said radiation to the patient's skin.
19. A system as claimed in claim 17 wherein said controls detect a temperature profile at said sensor, said profile being indicative of contact of said waveguide with the patient's skin, and wherein said controls prevent said radiation from passing to the patient's skin unless a predetermined profile is detected.
20. A system as claimed in claim 17 wherein said controls operate said mechanism to cool said waveguide to a desired temperature, and wherein said controls are responsive to said sensor for determining when said temperature has been reached.
21. A system as claimed in claim 16 wherein said sensor is located no more than a few millimeters from the second end of said waveguide.
22. A system as claimed in claim 16 wherein said second end of the waveguide has an aperture at least substantially as great as the aperture of radiation back-scattered from the patient's skin.
23. A system as claimed in claim 22 wherein back-scattered radiation is substantially internally reflected within said waveguide; and including a reflector within said waveguide for returning back-scattered radiation through the waveguide to the patient's skin.
24. A system as claimed in claim 23 wherein said reflector is at said first end of the waveguide.
25. A system as claimed is claim 24 wherein said reflector is also along at least a portion of waveguide sidewalk, and wherein said reflector has a coefficient of reflection at areas thereof such that backscattered radiation at angles nearer perpendicular to said skin contacting second end are reflected more strongly then back scattered radiation at angles nearer parallel to said second end.
26. A system for treating a selected dermatologic problem located in a selected volume of a patient's skin at a depth d, which depth is below the DE junction, comprising:
a source of E.M radiation of a wavelength appropriate for treating said problem;
an optical waveguide having a first end at which said radiation is applied and a second end for contacting the patient's skin, which second end is opposite said first end;
a mechanism which cools the patient's skin, at least in the portion thereof in contract with said waveguide, when said second end is in contact with the patient's skin;
a temperature sensor at said second end of the waveguide, the temperature at said sensor being indicaxive of the temperantre at the patient's DE junction; and controls operative in response the sensor sensing a selected increasing temperature profile at the sensor when the waveguidc is placed in contact with the patient's skin for permitting radiation from said source to be passed tluough said waveguide to the patient's skin, including said selected volume.
a source of E.M radiation of a wavelength appropriate for treating said problem;
an optical waveguide having a first end at which said radiation is applied and a second end for contacting the patient's skin, which second end is opposite said first end;
a mechanism which cools the patient's skin, at least in the portion thereof in contract with said waveguide, when said second end is in contact with the patient's skin;
a temperature sensor at said second end of the waveguide, the temperature at said sensor being indicaxive of the temperantre at the patient's DE junction; and controls operative in response the sensor sensing a selected increasing temperature profile at the sensor when the waveguidc is placed in contact with the patient's skin for permitting radiation from said source to be passed tluough said waveguide to the patient's skin, including said selected volume.
27. A system 10 utilizing the head 16 of any of claims 30-37, said system including:
a source 12 of EM radiation of a wavelength appropriate for treating said problem, radiation from said source being applied to said first end of the waveguide;
and controls 20 for selectively permitting radiation from said source to be passed through said waveguide to the patient's skin, including said selected volume.
a source 12 of EM radiation of a wavelength appropriate for treating said problem, radiation from said source being applied to said first end of the waveguide;
and controls 20 for selectively permitting radiation from said source to be passed through said waveguide to the patient's skin, including said selected volume.
28. (cancelled)
29. (cancelled)
30. A head 16 as claimed in claim 38 wherein said at least one light path includes an optical waveguide 40, and a light path 58 for directing the EM radiation to a first end of the waveguide, said waveguide having said skin-contacting surface as a second end which is opposite said first end, said secaed end of the waveguide being at least part of a reflection aperture D at least substantially as great as said back-scatter aperture, back-scattered radiation entering the waveguide being substantially internally reflected within said waveguide; and a reflector 76, ctc. within said waveguide far returning the back-scattered radiation entering the waveguide through the waveguide to the patients skin.
31. A head 16 as claimed in claim 30 wherein said reflector is at said first end of the waveguide.
32. A head 16 as claimed in claim 31 wherein said reflector is also along at least a portion of waveguide sidewalls, and wherein said reflector has a coefficient of reflection at areas thereof such that backscartered radiation entering the waveguide at angles nearer perpendicular to said skin contacting second end are reflected more strongly then back scattered radiation entering at angles nearer parallel to said second end.
33. A head 16 as claimed in claim 30 wherein said waveguide is cooled, and means for maintaining a moisture-free environment for said reflector to inhibit condensation thereon.
34. A head 16 as claimed in claim 30 wherein said second end of the waveguide has an aperture D at least substantially as great as the aperture of radiation back-scattered from the patient's skin.
35. A head 16 as claimed in claim 30 including a reflector plate 97 surrounding said waveguide 40 at the second end thereof, the combined area of the plate and the waveguide projecting therethrough being substantially equal to the aperture of radiation back-scatter.
36. A head 16 as claimed in claim 35 wherein said plate 97 has a concave shape.
37. A head 16 as claimed in claim 35 including a means 99 far controlling the temperature of the plate.
38. A head 16 for applying EM radiation 28 of a wavelength appropriate for treating a selected patient dermatologic problem at a selected volume 30 of a patient's skin 18, the head comprising:
a skin-contacting surface;
at least one light path passing through said head and terminating at said skin-contacting surface. said EM radiation being applied through said at least one light path to the patient's skin;
some of the radiation passing through the waveguide to a patient's skin being back-scattered over a back-scatter aperture, sand held including reflection means for returning back-scattered radiation to the patient's skin, said reflection means having a reflection aperture D at least substantially as great as said back-scatter aperture.
a skin-contacting surface;
at least one light path passing through said head and terminating at said skin-contacting surface. said EM radiation being applied through said at least one light path to the patient's skin;
some of the radiation passing through the waveguide to a patient's skin being back-scattered over a back-scatter aperture, sand held including reflection means for returning back-scattered radiation to the patient's skin, said reflection means having a reflection aperture D at least substantially as great as said back-scatter aperture.
39. A head 16 as claimed in claim 38 wherein said reflection means includes at least a portion of said skin-contacting surface being formed as a reflection plate 97.
40. A head 16 as claimed in claim 39 wherein some of the back-scattered radiation enters said light path, and wherein said reflection means includes at least one reflection surface 74, 76, etc.
for the back-scattered radiation entering the light path.
for the back-scattered radiation entering the light path.
41. A head as claimed in claim 40 wherein at least a part of said at least one reflection surface is in said light path.
42. A head for applying EM radiation of a wavelength appropriate for treating a selected patient dermatoiogic problem at a selected volume of a patient's skin, the head comprising:
at least on optical waveguide for receiving said EM radiation and for directing it to a skin-contacting surface of the at least one waveguide;
a standoff having a first and second end, the first end surrounding said at least one waveguide at its lower and and forming a substantially air-tight seal therewith, and said second end being adapted to contact the patient's skin over said selected volume to form a chamber between said skin-contacting waveguide surface, the patient's skin and walls of the standoff;
and means for creating negative pressure in said chamber to draw the patient's skin therein and into contact with said skin-contacting surface.
at least on optical waveguide for receiving said EM radiation and for directing it to a skin-contacting surface of the at least one waveguide;
a standoff having a first and second end, the first end surrounding said at least one waveguide at its lower and and forming a substantially air-tight seal therewith, and said second end being adapted to contact the patient's skin over said selected volume to form a chamber between said skin-contacting waveguide surface, the patient's skin and walls of the standoff;
and means for creating negative pressure in said chamber to draw the patient's skin therein and into contact with said skin-contacting surface.
43. A head as claimed in claim 42 wherein the walls of said standoff are reflective to return back-scattered radiation to the patient's skin.
44. A head as claimed in claim 42 wherein said means for creating negative pressure includes a hale mounted at one end to open into said chamber and connected at its other end to a source of negative pressure.
45. A head as claimed in claim 42 wherein said means for creating negative pressure includes the walls of said standoffbeing deformable when pressure is applied to the waveguide to permit the skin-contacting surface of the waveguide to contact the patient's skin, forcing most of the air from said chamber, said walls returning to their undeformed state when pressure is released resulting in the creation of negative pressure in said chamber.
46. A head as claimed in claim 45 wherein said walls of the standoff arc in the form of a bellows.
47. A head as claimed in claim 45 wherein said walls of the standoff are in the form of a suction cup.
48. A head as claimed in claim 45 wherein said walls of the standoff are in the form of a classic ring.
49. A head for applying EM radiation of a wavelength appropriate for treating a selected patient dermatologic problem at a selected volume of a patient's skin, the head comprising:
at least one first optical waveguide for receiving said EM radiation and for directing it to a output surface of the at least one waveguide; and a second optical waveguide having a first surface mounted to the output surface of the first optical waveguide to receive said EM radiation therefrom and having a second skin-contacting surface opposite said first surface, said skin-contacting surface having a larger area than said output surface and said second waveguide being formed to provide a larger optical aperture than that of said first waveguide.
at least one first optical waveguide for receiving said EM radiation and for directing it to a output surface of the at least one waveguide; and a second optical waveguide having a first surface mounted to the output surface of the first optical waveguide to receive said EM radiation therefrom and having a second skin-contacting surface opposite said first surface, said skin-contacting surface having a larger area than said output surface and said second waveguide being formed to provide a larger optical aperture than that of said first waveguide.
50. A head as claimed in claim 49 wherein the ratio of the spacing between said first and second surfaces of the second waveguide and a selected surface dimension of said second surface is approximately 1.5 to 1Ø
51. A head as claimed in claim 50 wherein said selected surface dimension is one of the length of a side of said second surface and a diameter of said second surface.
52. A head as claimed in claim 49 including means for reflecting radiation back-scattered fmrn the patient's skin into said second waveguide back into the patient's skin.
53. A head as claimed in claim 52 wherein said means for reflecting including forming at last a portion of said first sutfact so as to reflect radiation impinging thereon.
54. A head as claimed in claim 53 wherein said reflector is also along at least a portion of waveguide sidewalls, and wherein said reflector has a coefficient of reflection at areas thereof such that backscartered radiation entering the waveguide at angles nearer perpendicular to said skin contacting surface are reflected more strongly then back scattered radiation entering at angles nearer parallel to said skin contacting surface.
55. A head 16, 110 for applying EM radiation 28 of a wavelength appropriate for treating a selected patient dermatologic problem at a selected volume 30 of a patient's skin 18, the head including:
a skin-contacting surface;
at least one light path 40, 114 passing through said head and terminating at said skin-contacting surface, said EM radiation being applied through said at least one light path to the patient's skin; and a temperature sensor 46, 124, 128 located in said head within less than 5 millimeters of said skin contacting surface.
a skin-contacting surface;
at least one light path 40, 114 passing through said head and terminating at said skin-contacting surface, said EM radiation being applied through said at least one light path to the patient's skin; and a temperature sensor 46, 124, 128 located in said head within less than 5 millimeters of said skin contacting surface.
56. (cancelled)
57. A head 16, 110 as claimed in claim 55 wherein said head is moved across a patient's skin 18 during treatment, and including a head portion 116 of a thermally conductive material passing over the skin prior to said at least one light path, a said temperature sensor 124 being located in said head portion.
58. A head 16, 110 as claimed in claim 57 including means 122 for one of heating and cooling said head portion 116 to preheat/precool the patient's skin prior to application of EM
radiation 28 thereto.
radiation 28 thereto.
59. A head 16, 110 as claimed in claim 57 including means 126 for heating said head portion to preheat the patients skin prior to application of EM radiation thereto, and means for utilizing the output of said temperature sensor 128 in response to the preheating to determine patient skin type.
Applications Claiming Priority (7)
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US7779498P | 1998-03-12 | 1998-03-12 | |
US60/077,794 | 1998-03-12 | ||
US60/078,055 | 1998-05-13 | ||
US09/078,055 US6273884B1 (en) | 1997-05-15 | 1998-05-13 | Method and apparatus for dermatology treatment |
US11544799P | 1999-01-08 | 1999-01-08 | |
US60/115,447 | 1999-01-08 | ||
PCT/US1999/005501 WO1999046005A1 (en) | 1998-03-12 | 1999-03-12 | System for electromagnetic radiation of the skin |
Publications (1)
Publication Number | Publication Date |
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CA2323479A1 true CA2323479A1 (en) | 1999-09-16 |
Family
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Application Number | Title | Priority Date | Filing Date |
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CA002323479A Abandoned CA2323479A1 (en) | 1998-03-12 | 1999-03-12 | System for electromagnetic radiation of the skin |
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US (4) | US6508813B1 (en) |
EP (2) | EP1566149A1 (en) |
AU (1) | AU3450799A (en) |
CA (1) | CA2323479A1 (en) |
DE (1) | DE69926348T2 (en) |
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WO (1) | WO1999046005A1 (en) |
Families Citing this family (290)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7229436B2 (en) * | 1996-01-05 | 2007-06-12 | Thermage, Inc. | Method and kit for treatment of tissue |
US7006874B2 (en) * | 1996-01-05 | 2006-02-28 | Thermage, Inc. | Treatment apparatus with electromagnetic energy delivery device and non-volatile memory |
US7141049B2 (en) * | 1999-03-09 | 2006-11-28 | Thermage, Inc. | Handpiece for treatment of tissue |
US7473251B2 (en) * | 1996-01-05 | 2009-01-06 | Thermage, Inc. | Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient |
US20030212393A1 (en) * | 1996-01-05 | 2003-11-13 | Knowlton Edward W. | Handpiece with RF electrode and non-volatile memory |
US20040000316A1 (en) * | 1996-01-05 | 2004-01-01 | Knowlton Edward W. | Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient |
US7267675B2 (en) * | 1996-01-05 | 2007-09-11 | Thermage, Inc. | RF device with thermo-electric cooler |
US7115123B2 (en) * | 1996-01-05 | 2006-10-03 | Thermage, Inc. | Handpiece with electrode and non-volatile memory |
US6273884B1 (en) | 1997-05-15 | 2001-08-14 | Palomar Medical Technologies, Inc. | Method and apparatus for dermatology treatment |
US20060149343A1 (en) * | 1996-12-02 | 2006-07-06 | Palomar Medical Technologies, Inc. | Cooling system for a photocosmetic device |
US6517532B1 (en) * | 1997-05-15 | 2003-02-11 | Palomar Medical Technologies, Inc. | Light energy delivery head |
US6653618B2 (en) | 2000-04-28 | 2003-11-25 | Palomar Medical Technologies, Inc. | Contact detecting method and apparatus for an optical radiation handpiece |
US8182473B2 (en) * | 1999-01-08 | 2012-05-22 | Palomar Medical Technologies | 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 |
US6074382A (en) | 1997-08-29 | 2000-06-13 | Asah Medico A/S | Apparatus for tissue treatment |
AUPP176898A0 (en) * | 1998-02-12 | 1998-03-05 | Moldflow Pty Ltd | Automated machine technology for thermoplastic injection molding |
EP1566149A1 (en) | 1998-03-12 | 2005-08-24 | Palomar Medical Technologies, Inc. | System for electromagnetic radiation of the skin |
ES2403359T3 (en) * | 1998-03-27 | 2013-05-17 | The General Hospital Corporation | Procedure and apparatus for the selective determination of lipid rich tissues |
JPH11318922A (en) * | 1998-05-11 | 1999-11-24 | Kaihatsu Komonshitsu:Kk | Laser depilating method, skin holding implement, glove, fingerstall and thumbstall |
US6059820A (en) | 1998-10-16 | 2000-05-09 | Paradigm Medical Corporation | Tissue cooling rod for laser surgery |
US9192780B2 (en) | 1998-11-30 | 2015-11-24 | L'oreal | Low intensity light therapy for treatment of retinal, macular, and visual pathway disorders |
US20060212025A1 (en) | 1998-11-30 | 2006-09-21 | Light Bioscience, Llc | Method and apparatus for acne treatment |
US6887260B1 (en) | 1998-11-30 | 2005-05-03 | Light Bioscience, Llc | Method and apparatus for acne treatment |
US6514242B1 (en) * | 1998-12-03 | 2003-02-04 | David Vasily | Method and apparatus for laser removal of hair |
AU3147200A (en) | 1999-03-08 | 2000-09-28 | Asah Medico A/S | An apparatus for tissue treatment and having a monitor for display of tissue features |
US20020156471A1 (en) * | 1999-03-09 | 2002-10-24 | Stern Roger A. | Method for treatment of tissue |
US7041094B2 (en) * | 1999-03-15 | 2006-05-09 | Cutera, Inc. | Tissue treatment device and method |
AU2002359840A1 (en) * | 1999-06-30 | 2003-07-09 | Thermage, Inc. | Liquid cooled RF handpiece |
JP2001190565A (en) * | 2000-01-06 | 2001-07-17 | Slt Japan:Kk | Laser beam irradiation system to living body |
IL150604A0 (en) * | 2000-01-25 | 2003-02-12 | Palomar Medical Tech Inc | Method and apparatus for medical treatment utilizing long duration electromagnetic radiation |
US7780654B2 (en) | 2000-02-23 | 2010-08-24 | Asclepion Laser Technologies Gmbh | Device for radiating light onto a skin surface during a medical or cosmetic skin treatment |
AU2002245163A1 (en) * | 2000-10-20 | 2002-07-24 | Photomedex | Controlled dose delivery of ultraviolet light for treating skin disorders |
JP2005502385A (en) * | 2000-12-28 | 2005-01-27 | パロマー・メディカル・テクノロジーズ・インコーポレーテッド | Method and apparatus for performing skin therapy EMR treatment |
US20080183162A1 (en) * | 2000-12-28 | 2008-07-31 | Palomar Medical Technologies, Inc. | Methods And Devices For Fractional Ablation Of Tissue |
US6888319B2 (en) * | 2001-03-01 | 2005-05-03 | Palomar Medical Technologies, Inc. | Flashlamp drive circuit |
EP1665996A3 (en) * | 2001-03-02 | 2007-11-28 | Palomar Medical Technologies, Inc. | Apparatus and method for photocosmetic and photodermatological treatment |
AU2002316500A1 (en) | 2001-07-02 | 2003-01-21 | Palomar Medical Technologies, Inc. | Laser device for medical/cosmetic procedures |
US7144248B2 (en) * | 2001-10-18 | 2006-12-05 | Irwin Dean S | Device for oral UV photo-therapy |
US9993659B2 (en) | 2001-11-01 | 2018-06-12 | Pthera, Llc | Low level light therapy for enhancement of neurologic function by altering axonal transport rate |
US7534255B1 (en) | 2003-01-24 | 2009-05-19 | Photothera, Inc | Low level light therapy for enhancement of neurologic function |
US10683494B2 (en) | 2001-11-01 | 2020-06-16 | Pthera LLC | Enhanced stem cell therapy and stem cell production through the administration of low level light energy |
US7303578B2 (en) | 2001-11-01 | 2007-12-04 | Photothera, Inc. | Device and method for providing phototherapy to the brain |
US20040147984A1 (en) * | 2001-11-29 | 2004-07-29 | Palomar Medical Technologies, Inc. | Methods and apparatus for delivering low power optical treatments |
US7762965B2 (en) * | 2001-12-10 | 2010-07-27 | Candela Corporation | Method and apparatus for vacuum-assisted light-based treatments of the skin |
US7935139B2 (en) * | 2001-12-10 | 2011-05-03 | Candela Corporation | Eye safe dermatological phototherapy |
US7762964B2 (en) | 2001-12-10 | 2010-07-27 | Candela Corporation | Method and apparatus for improving safety during exposure to a monochromatic light source |
EP1627662B1 (en) | 2004-06-10 | 2011-03-02 | Candela Corporation | Apparatus for vacuum-assisted light-based treatments of the skin |
WO2003049633A1 (en) | 2001-12-10 | 2003-06-19 | Inolase 2002 Ltd. | Method and apparatus for improving safety during exposure to a monochromatic light source |
US20030109860A1 (en) * | 2001-12-12 | 2003-06-12 | Michael Black | Multiple laser treatment |
US20040082940A1 (en) * | 2002-10-22 | 2004-04-29 | Michael Black | Dermatological apparatus and method |
US20030109787A1 (en) * | 2001-12-12 | 2003-06-12 | Michael Black | Multiple laser diagnostics |
US10695577B2 (en) * | 2001-12-21 | 2020-06-30 | Photothera, Inc. | Device and method for providing phototherapy to the heart |
AU2002367397A1 (en) * | 2001-12-27 | 2003-07-24 | Palomar Medical Technologies, Inc. | Method and apparatus for improved vascular related treatment |
IL163946A0 (en) * | 2002-03-12 | 2005-12-18 | Gen Hospital Corp | Method and apparatus for hair growth managment |
US7056318B2 (en) * | 2002-04-12 | 2006-06-06 | Reliant Technologies, Inc. | Temperature controlled heating device and method to heat a selected area of a biological body |
US20070038206A1 (en) * | 2004-12-09 | 2007-02-15 | Palomar Medical Technologies, Inc. | Photocosmetic device |
US7135033B2 (en) * | 2002-05-23 | 2006-11-14 | Palomar Medical Technologies, Inc. | Phototreatment device for use with coolants and topical substances |
AU2002325533A1 (en) | 2002-05-31 | 2003-12-19 | Ya-Man Ltd. | Laser depilator |
BR0312430A (en) | 2002-06-19 | 2005-04-26 | Palomar Medical Tech Inc | Method and apparatus for treating skin and subcutaneous conditions |
JP2006500972A (en) * | 2002-06-19 | 2006-01-12 | 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 | Method and apparatus for treating tissue at a depth by radiant heat |
US7740600B2 (en) | 2002-08-02 | 2010-06-22 | Candela Corporation | Apparatus and method for inhibiting pain signals transmitted during a skin related medical treatment |
US7250047B2 (en) * | 2002-08-16 | 2007-07-31 | Lumenis Ltd. | System and method for treating tissue |
US8506979B2 (en) | 2002-08-28 | 2013-08-13 | Nomir Medical Technologies, Inc. | Near-infrared electromagnetic modification of cellular steady-state membrane potentials |
US20080131968A1 (en) * | 2002-08-28 | 2008-06-05 | Nomir Medical Technologies, Inc. | Near-infrared electromagnetic modification of cellular steady-state membrane potentials |
WO2007014130A2 (en) * | 2005-07-21 | 2007-02-01 | Nomir Medical Technologies, Inc. | Near infrared microbial elimination laser system (nimels) |
US7713294B2 (en) | 2002-08-28 | 2010-05-11 | Nomir Medical Technologies, Inc. | Near infrared microbial elimination laser systems (NIMEL) |
US20040126272A1 (en) * | 2002-08-28 | 2004-07-01 | Eric Bornstein | Near infrared microbial elimination laser system |
US20040156743A1 (en) * | 2002-08-28 | 2004-08-12 | Eric Bornstein | Near infrared microbial elimination laser system |
WO2004033040A1 (en) * | 2002-10-07 | 2004-04-22 | Palomar Medical Technologies, Inc. | Apparatus for performing photobiostimulation |
US6916315B2 (en) * | 2002-10-07 | 2005-07-12 | Kenneth Lawrence Short | Methods of operating a photo-thermal epilation apparatus |
US20070213792A1 (en) * | 2002-10-07 | 2007-09-13 | Palomar Medical Technologies, Inc. | Treatment Of Tissue Volume With Radiant Energy |
US20070219605A1 (en) * | 2006-03-20 | 2007-09-20 | Palomar Medical Technologies, Inc. | Treatment of tissue volume with radiant energy |
US7931028B2 (en) | 2003-08-26 | 2011-04-26 | Jay Harvey H | Skin injury or damage prevention method using optical radiation |
WO2004043543A1 (en) * | 2002-11-12 | 2004-05-27 | Palomar Medical Technologies, Inc. | Apparatus for performing optical dermatology |
US7255560B2 (en) * | 2002-12-02 | 2007-08-14 | Nomir Medical Technologies, Inc. | Laser augmented periodontal scaling instruments |
AU2003301111A1 (en) * | 2002-12-20 | 2004-07-22 | Palomar Medical Technologies, Inc. | Apparatus for light treatment of acne and other disorders of follicles |
JP2006518266A (en) * | 2003-02-19 | 2006-08-10 | 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 | Method and apparatus for treating fake folliculitis |
US20040176754A1 (en) * | 2003-03-06 | 2004-09-09 | Island Tobin C. | Method and device for sensing skin contact |
ES2570985T3 (en) * | 2003-02-25 | 2016-05-23 | Tria Beauty Inc | Apparatus and procedure for inhibiting new hair growth, safe for the eye and autonomous |
US20040176823A1 (en) * | 2003-02-25 | 2004-09-09 | Island Tobin C. | Acne treatment device and method |
WO2004077020A2 (en) * | 2003-02-25 | 2004-09-10 | Spectragenics, Inc. | Skin sensing method and apparatus |
EP2604216B1 (en) * | 2003-02-25 | 2018-08-22 | Tria Beauty, Inc. | Self-contained, diode-laser-based dermatologic treatment apparatus |
US8709003B2 (en) * | 2003-02-25 | 2014-04-29 | Tria Beauty, Inc. | Capacitive sensing method and device for detecting skin |
WO2004075721A2 (en) * | 2003-02-25 | 2004-09-10 | Spectragenics, Inc. | Self-contained, diode-laser-based dermatologic treatment apparatus and metod |
US20100069898A1 (en) * | 2003-02-25 | 2010-03-18 | Tria Beauty, Inc. | Acne Treatment Method, System and Device |
US7981111B2 (en) | 2003-02-25 | 2011-07-19 | Tria Beauty, Inc. | Method and apparatus for the treatment of benign pigmented lesions |
JP4361081B2 (en) * | 2003-02-25 | 2009-11-11 | トリア ビューティ インコーポレイテッド | Eye-safe dermatological treatment device |
US20040176824A1 (en) * | 2003-03-04 | 2004-09-09 | Weckwerth Mark V. | Method and apparatus for the repigmentation of human skin |
DE202004021226U1 (en) * | 2003-03-27 | 2007-07-26 | The General Hospital Corp., Boston | Device for dermatological treatment and fractional surface renewal of the skin |
US7144247B2 (en) * | 2003-04-25 | 2006-12-05 | Oralum, Llc | Hygienic treatments of structures in body cavities |
US6989023B2 (en) * | 2003-07-08 | 2006-01-24 | Oralum, Llc | Hygienic treatments of body structures |
US20060183072A1 (en) * | 2003-04-25 | 2006-08-17 | Michael Black | Device for application of multiple hygienic effects |
US7470124B2 (en) * | 2003-05-08 | 2008-12-30 | Nomir Medical Technologies, Inc. | Instrument for delivery of optical energy to the dental root canal system for hidden bacterial and live biofilm thermolysis |
WO2005007003A1 (en) * | 2003-07-11 | 2005-01-27 | Reliant Technologies, Inc. | Method and apparatus for fractional photo therapy of skin |
US7291140B2 (en) * | 2003-07-18 | 2007-11-06 | Cutera, Inc. | System and method for low average power dermatologic light treatment device |
US8623002B2 (en) * | 2003-07-29 | 2014-01-07 | Koninklijke Philips N.V. | Electromagnetic radiation delivery apparatus |
WO2005011606A2 (en) | 2003-07-31 | 2005-02-10 | Light Bioscience, Llc | System and method for the photodynamic treatment of burns, wounds, and related skin disorders |
CN100577236C (en) * | 2003-08-18 | 2010-01-06 | 皇家飞利浦电子股份有限公司 | Device and method for low intensity optical hair growth control |
US8915906B2 (en) * | 2003-08-25 | 2014-12-23 | Cutera, Inc. | Method for treatment of post-partum abdominal skin redundancy or laxity |
US7722600B2 (en) | 2003-08-25 | 2010-05-25 | Cutera, Inc. | System and method for heating skin using light to provide tissue treatment |
US8870856B2 (en) | 2003-08-25 | 2014-10-28 | Cutera, Inc. | Method for heating skin using light to provide tissue treatment |
GB0324254D0 (en) * | 2003-10-16 | 2003-11-19 | Euphotonics Ltd | Apparatus for illuminating a zone of mammalian skin |
US20080172045A1 (en) * | 2003-10-24 | 2008-07-17 | Shanks Steven C | Acne treatment device |
US7326199B2 (en) * | 2003-12-22 | 2008-02-05 | Cutera, Inc. | System and method for flexible architecture for dermatologic treatments utilizing multiple light sources |
US7282060B2 (en) | 2003-12-23 | 2007-10-16 | Reliant Technologies, Inc. | Method and apparatus for monitoring and controlling laser-induced tissue treatment |
US7184184B2 (en) * | 2003-12-31 | 2007-02-27 | Reliant Technologies, Inc. | High speed, high efficiency optical pattern generator using rotating optical elements |
US7372606B2 (en) | 2003-12-31 | 2008-05-13 | Reliant Technologies, Inc. | Optical pattern generator using a single rotating component |
US7220254B2 (en) * | 2003-12-31 | 2007-05-22 | 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 |
US7196831B2 (en) * | 2003-12-31 | 2007-03-27 | Reliant Technologies, Inc. | Two-dimensional optical scan system using a counter-rotating disk scanner |
US8777935B2 (en) * | 2004-02-25 | 2014-07-15 | Tria Beauty, Inc. | Optical sensor and method for identifying the presence of skin |
JP5065005B2 (en) | 2004-04-01 | 2012-10-31 | ザ ジェネラル ホスピタル コーポレイション | Method and apparatus for dermatological treatment and tissue remodeling |
US20080132886A1 (en) * | 2004-04-09 | 2008-06-05 | Palomar Medical Technologies, Inc. | Use of fractional emr technology on incisions and internal tissues |
WO2005099369A2 (en) * | 2004-04-09 | 2005-10-27 | Palomar Medical Technologies, Inc. | Emr treated islets |
US20070179482A1 (en) * | 2004-05-07 | 2007-08-02 | Anderson Robert S | Apparatuses and methods to treat biological external tissue |
US20050251117A1 (en) * | 2004-05-07 | 2005-11-10 | Anderson Robert S | Apparatus and method for treating biological external tissue |
US8571648B2 (en) * | 2004-05-07 | 2013-10-29 | Aesthera | Apparatus and method to apply substances to tissue |
US7842029B2 (en) * | 2004-05-07 | 2010-11-30 | Aesthera | Apparatus and method having a cooling material and reduced pressure to treat biological external tissue |
US7413572B2 (en) * | 2004-06-14 | 2008-08-19 | Reliant Technologies, Inc. | Adaptive control of optical pulses for laser medicine |
US7837675B2 (en) * | 2004-07-22 | 2010-11-23 | Shaser, Inc. | Method and device for skin treatment with replaceable photosensitive window |
ES2432140T3 (en) * | 2004-08-06 | 2013-11-29 | Syneron Beauty Ltd. | Therapy device |
US20060047281A1 (en) | 2004-09-01 | 2006-03-02 | Syneron Medical Ltd. | Method and system for invasive skin treatment |
US20110015549A1 (en) * | 2005-01-13 | 2011-01-20 | Shimon Eckhouse | Method and apparatus for treating a diseased nail |
US20060253176A1 (en) * | 2005-02-18 | 2006-11-09 | Palomar Medical Technologies, Inc. | Dermatological treatment device with deflector optic |
US20060271028A1 (en) * | 2005-02-18 | 2006-11-30 | Palomar Medical Technologies, Inc. | Dermatological treatment device |
CN101115449B (en) * | 2005-03-02 | 2011-12-07 | 美体安有限公司 | Adipose resolve apparatus for low-power laser |
US8540701B2 (en) * | 2005-03-04 | 2013-09-24 | The Invention Science Fund I, Llc | Hair treatment system |
US8679101B2 (en) * | 2005-03-04 | 2014-03-25 | The Invention Science Fund I, Llc | Method and system for temporary hair removal |
US8529560B2 (en) | 2005-03-04 | 2013-09-10 | The Invention Science Fund I, Llc | Hair treatment system |
US8157807B2 (en) * | 2005-06-02 | 2012-04-17 | The Invention Science Fund I, Llc | Skin treatment including patterned light |
US20060200114A1 (en) * | 2005-03-04 | 2006-09-07 | Searete Llc, A Limited Liability Corporation Of State Of Delaware | Hair removal system with light source array |
US20060276859A1 (en) * | 2005-06-02 | 2006-12-07 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Photopatterning of skin |
US7975702B2 (en) * | 2005-04-05 | 2011-07-12 | El.En. S.P.A. | System and method for laser lipolysis |
US7856985B2 (en) | 2005-04-22 | 2010-12-28 | Cynosure, Inc. | Method of treatment body tissue using a non-uniform laser beam |
US20070032846A1 (en) * | 2005-08-05 | 2007-02-08 | Bran Ferren | Holographic tattoo |
BRPI0520318A2 (en) * | 2005-06-13 | 2009-09-15 | Koninkl Philips Electronics Nv | tissue treatment electromagnetic radiation dispensing apparatus |
US9055958B2 (en) * | 2005-06-29 | 2015-06-16 | The Invention Science Fund I, Llc | Hair modification using converging light |
US20070038270A1 (en) * | 2005-07-05 | 2007-02-15 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Multi step photopatterning of skin |
EP1912585A2 (en) * | 2005-08-05 | 2008-04-23 | Koninklijke Philips Electronics N.V. | Skin-treatment device |
FR2889439B1 (en) * | 2005-08-05 | 2008-10-31 | Eurofeedback Sa | HANDPIECE FOR TREATMENT APPARATUS BY TRANSMITTING LIGHT FLASKS |
AU2006278255A1 (en) * | 2005-08-08 | 2007-02-15 | Palomar Medical Technologies, Inc. | Eye-safe photocosmetic device |
AU2006279865B8 (en) * | 2005-08-12 | 2013-01-31 | Board Of Regents, The University Of Texas System | Systems, devices, and methods for optically clearing tissue |
WO2007027962A2 (en) * | 2005-08-29 | 2007-03-08 | Reliant Technologies, Inc. | Method and apparatus for monitoring and controlling thermally induced tissue treatment |
US20070048340A1 (en) * | 2005-08-31 | 2007-03-01 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Multi step patterning of a skin surface |
JP2009509140A (en) | 2005-09-15 | 2009-03-05 | パロマー・メデイカル・テクノロジーズ・インコーポレーテツド | Skin optical determination device |
US8048089B2 (en) | 2005-12-30 | 2011-11-01 | Edge Systems Corporation | Apparatus and methods for treating the skin |
EP1983888B1 (en) * | 2006-01-24 | 2014-06-25 | Nomir Medical Technologies, Inc | Optical device for modulation of biochemical processes in adipose tissue |
US20090254154A1 (en) | 2008-03-18 | 2009-10-08 | Luis De Taboada | Method and apparatus for irradiating a surface with pulsed light |
US7575589B2 (en) * | 2006-01-30 | 2009-08-18 | Photothera, Inc. | Light-emitting device and method for providing phototherapy to the brain |
US10357662B2 (en) | 2009-02-19 | 2019-07-23 | Pthera LLC | Apparatus and method for irradiating a surface with light |
US20070179570A1 (en) * | 2006-01-30 | 2007-08-02 | Luis De Taboada | Wearable device and method for providing phototherapy to the brain |
CA2535276A1 (en) * | 2006-02-06 | 2007-08-06 | John Kennedy | Therapy device and system and method for reducing harmful exposure to electromagnetic radiation |
US20070194717A1 (en) * | 2006-02-17 | 2007-08-23 | Palomar Medical Technologies, Inc. | Lamp for use in a tissue treatment device |
US7854754B2 (en) | 2006-02-22 | 2010-12-21 | Zeltiq Aesthetics, Inc. | Cooling device for removing heat from subcutaneous lipid-rich cells |
KR100799524B1 (en) * | 2006-02-28 | 2008-01-31 | 전용규 | An applicator in a device for treating skin |
US7657147B2 (en) * | 2006-03-02 | 2010-02-02 | Solar Light Company, Inc. | Sunlight simulator apparatus |
WO2007106856A2 (en) * | 2006-03-14 | 2007-09-20 | Allux Medical, Inc. | Phototherapy device and method of providing phototherapy to a body surface |
US20070271714A1 (en) * | 2006-03-17 | 2007-11-29 | Light Dimensions, Inc. | Light-based enhancing apparatuses and methods of use |
WO2014151104A1 (en) | 2013-03-15 | 2014-09-25 | Edge Systems Llc | Devices, systems and methods for treating the skin |
US9566088B2 (en) | 2006-03-29 | 2017-02-14 | Edge Systems Llc | Devices, systems and methods for treating the skin |
US20070255355A1 (en) * | 2006-04-06 | 2007-11-01 | Palomar Medical Technologies, Inc. | Apparatus and method for skin treatment with compression and decompression |
WO2007129424A1 (en) * | 2006-04-14 | 2007-11-15 | Sumitomo Electric Industries, Ltd. | Treatment device and treatment method |
WO2007118303A2 (en) * | 2006-04-18 | 2007-10-25 | Daniel Barolet | Method for the treatment of skin tissues |
AU2007244765A1 (en) * | 2006-04-28 | 2007-11-08 | Zeltiq Aesthetics, Inc. | Cryoprotectant for use with a treatment device for improved cooling of subcutaneous lipid-rich cells |
US8460280B2 (en) * | 2006-04-28 | 2013-06-11 | Cutera, Inc. | Localized flashlamp skin treatments |
US8246611B2 (en) * | 2006-06-14 | 2012-08-21 | Candela Corporation | Treatment of skin by spatial modulation of thermal heating |
DE102006027788A1 (en) * | 2006-06-16 | 2007-12-20 | Braun Gmbh | Method of local heating of objects |
US7586957B2 (en) | 2006-08-02 | 2009-09-08 | Cynosure, Inc | Picosecond laser apparatus and methods for its operation and use |
US20080058782A1 (en) * | 2006-08-29 | 2008-03-06 | Reliant Technologies, Inc. | Method and apparatus for monitoring and controlling density of fractional tissue treatments |
EP2061395B1 (en) * | 2006-09-06 | 2010-10-27 | Shaser, Inc. | Scanning laser system for the treatment of tissue |
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 |
US9132031B2 (en) | 2006-09-26 | 2015-09-15 | Zeltiq Aesthetics, Inc. | Cooling device having a plurality of controllable cooling elements to provide a predetermined cooling profile |
US8192474B2 (en) * | 2006-09-26 | 2012-06-05 | Zeltiq Aesthetics, Inc. | Tissue treatment methods |
CN101528148A (en) * | 2006-10-23 | 2009-09-09 | 皇家飞利浦电子股份有限公司 | An optical treatment system and an adjustment member therefor |
US20080161782A1 (en) * | 2006-10-26 | 2008-07-03 | Reliant Technologies, Inc. | Micropore delivery of active substances |
JP2010509960A (en) * | 2006-11-18 | 2010-04-02 | ブラウン ゲーエムベーハー | Skin treatment device and accessories and handle part of skin treatment device |
EP2121122A2 (en) * | 2007-02-01 | 2009-11-25 | Candela Corporation | Biofeedback |
US20080186591A1 (en) * | 2007-02-01 | 2008-08-07 | Palomar Medical Technologies, Inc. | Dermatological device having a zoom lens system |
US20080188914A1 (en) * | 2007-02-01 | 2008-08-07 | Candela Corporation | Detachable handpiece |
RU2523620C2 (en) | 2007-04-19 | 2014-07-20 | Мирамар Лэбс,Инк. | Systems and methods for generating exposure on target tissue with using microwave energy |
EP2142129A4 (en) * | 2007-04-19 | 2011-04-20 | Miramar Labs Inc | Methods and apparatus for reducing sweat production |
EP2142125B1 (en) | 2007-04-19 | 2014-03-05 | Miramar Labs, Inc. | Devices, and systems for non-invasive delivery of microwave therapy |
WO2008131306A1 (en) | 2007-04-19 | 2008-10-30 | The Foundry, Inc. | Systems and methods for creating an effect using microwave energy to specified tissue |
US9241763B2 (en) * | 2007-04-19 | 2016-01-26 | Miramar Labs, Inc. | 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 |
US20080287839A1 (en) | 2007-05-18 | 2008-11-20 | Juniper Medical, Inc. | Method of enhanced removal of heat from subcutaneous lipid-rich cells and treatment apparatus having an actuator |
EP2155098A4 (en) * | 2007-06-08 | 2013-11-06 | Cynosure Inc | Thermal surgery safety apparatus and method |
US20090012434A1 (en) * | 2007-07-03 | 2009-01-08 | Anderson Robert S | Apparatus, method, and system to treat a volume of skin |
US20090018624A1 (en) * | 2007-07-13 | 2009-01-15 | Juniper Medical, Inc. | Limiting use of disposable system patient protection devices |
US20090018626A1 (en) * | 2007-07-13 | 2009-01-15 | Juniper Medical, Inc. | User interfaces for a system that removes heat from lipid-rich regions |
US20090018625A1 (en) * | 2007-07-13 | 2009-01-15 | Juniper Medical, Inc. | Managing system temperature to remove heat from lipid-rich regions |
US8523927B2 (en) * | 2007-07-13 | 2013-09-03 | Zeltiq Aesthetics, Inc. | System for treating lipid-rich regions |
ES2693430T3 (en) | 2007-08-21 | 2018-12-11 | Zeltiq Aesthetics, Inc. | Monitoring of cooling of lipid-rich subcutaneous cells, such as cooling of adipose tissue |
US20090069795A1 (en) * | 2007-09-10 | 2009-03-12 | Anderson Robert S | Apparatus and method for selective treatment of tissue |
US7740651B2 (en) | 2007-09-28 | 2010-06-22 | Candela Corporation | Vacuum assisted treatment of the skin |
US20090093864A1 (en) * | 2007-10-08 | 2009-04-09 | Anderson Robert S | Methods and devices for applying energy to tissue |
US20100274161A1 (en) * | 2007-10-15 | 2010-10-28 | Slender Medical, Ltd. | Implosion techniques for ultrasound |
US20090112063A1 (en) * | 2007-10-31 | 2009-04-30 | Bakos Gregory J | Endoscopic overtubes |
FR2924597B1 (en) * | 2007-12-10 | 2014-06-13 | Oreal | PROCESS FOR TREATING KERATIN FIBERS HAVING THEIR EXPOSURE TO LOW-LIFE LIGHT PULSES |
ES2471971T3 (en) | 2007-12-12 | 2014-06-27 | Miramar Labs, Inc. | System and apparatus for non-invasive treatment of tissue using microwave energy |
AU2008335715B2 (en) | 2007-12-12 | 2014-01-23 | Miradry, Inc. | Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy |
ES2301447B1 (en) * | 2007-12-17 | 2009-07-06 | S.O.R. Internacional, S.A. | GUN WITH LAMP FOR PHOTODEPILATION AND ELECTRODEPILATION. |
KR101836310B1 (en) | 2008-01-04 | 2018-03-08 | 엣지 시스템즈 엘엘씨 | Appratus and method for treating the skin |
AU2009205297A1 (en) | 2008-01-17 | 2009-07-23 | Syneron Medical Ltd. | A hair removal apparatus for personal use and the method of using same |
EP2237732A4 (en) | 2008-01-24 | 2011-06-01 | Syneron Medical Ltd | A device, apparatus, and method of adipose tissue treatment |
US8540702B2 (en) * | 2008-03-11 | 2013-09-24 | Shaser, Inc. | Enhancing the brightness of optical radiation used in light-based dermatologic treatment systems |
US7671327B2 (en) | 2008-04-22 | 2010-03-02 | Candela Corporation | Self calibrating irradiation system |
US9687671B2 (en) * | 2008-04-25 | 2017-06-27 | Channel Investments, Llc | Optical sensor and method for identifying the presence of skin and the pigmentation of skin |
US9675417B2 (en) * | 2008-07-15 | 2017-06-13 | Koninklijke Philips N.V. | Safe ablation |
US9314293B2 (en) * | 2008-07-16 | 2016-04-19 | Syneron Medical Ltd | RF electrode for aesthetic and body shaping devices and method of using same |
US20100017750A1 (en) * | 2008-07-16 | 2010-01-21 | Avner Rosenberg | User interface |
US8945104B2 (en) * | 2008-08-22 | 2015-02-03 | Envy Medical, Inc. | Microdermabrasion system with combination skin therapies |
JP5452601B2 (en) * | 2008-09-11 | 2014-03-26 | シネロン メディカル リミテッド | Safe personal skin treatment equipment |
US20110178541A1 (en) * | 2008-09-12 | 2011-07-21 | Slender Medical, Ltd. | Virtual ultrasonic scissors |
US7848035B2 (en) * | 2008-09-18 | 2010-12-07 | Photothera, Inc. | Single-use lens assembly |
ES2412783T3 (en) * | 2008-09-21 | 2013-07-12 | Syneron Medical Ltd. | A method and apparatus for personal skin treatment |
WO2010036732A1 (en) * | 2008-09-25 | 2010-04-01 | Zeltiq Aesthetics, Inc. | Treatment planning systems and methods for body contouring applications |
US8603073B2 (en) * | 2008-12-17 | 2013-12-10 | Zeltiq Aesthetics, Inc. | Systems and methods with interrupt/resume capabilities for treating subcutaneous lipid-rich cells |
US8130904B2 (en) | 2009-01-29 | 2012-03-06 | The Invention Science Fund I, Llc | Diagnostic delivery service |
US8031838B2 (en) | 2009-01-29 | 2011-10-04 | The Invention Science Fund I, Llc | Diagnostic delivery service |
US8606366B2 (en) | 2009-02-18 | 2013-12-10 | Syneron Medical Ltd. | Skin treatment apparatus for personal use and method for using same |
EP2730313A1 (en) | 2009-02-25 | 2014-05-14 | Syneron Medical Ltd. | Electrical skin rejuvenation |
WO2010127315A2 (en) | 2009-04-30 | 2010-11-04 | Zeltiq Aesthetics, Inc. | Device, system and method of removing heat from subcutaneous lipid-rich cells |
US8512322B1 (en) | 2009-05-01 | 2013-08-20 | Tria Beauty, Inc. | Antimicrobial layer for optical output window |
GB2470927A (en) * | 2009-06-10 | 2010-12-15 | Dezac Group Ltd | Phototherapy apparatus with skin temperature control |
US9919168B2 (en) | 2009-07-23 | 2018-03-20 | Palomar Medical Technologies, Inc. | Method for improvement of cellulite appearance |
US8518027B2 (en) * | 2009-10-28 | 2013-08-27 | Tria Beauty, Inc. | Phototherapy device thermal control apparatus and method |
US9302118B2 (en) | 2009-10-28 | 2016-04-05 | Tria Beauty, Inc. | Phototherapy device thermal control apparatus and method |
MX2012006497A (en) | 2009-12-06 | 2012-07-30 | Syneron Medical Ltd | A method and apparatus for personal skin treatment. |
KR20120113788A (en) * | 2010-01-25 | 2012-10-15 | 젤티크 애스세틱스, 인코포레이티드. | Home-use applicators for non-invasively removing heat from subcutaneous lipid-rich cells via phase change coolants, and associated devices, systems and methods |
US9427506B2 (en) * | 2010-03-31 | 2016-08-30 | Kci Licensing, Inc. | System and method for locating fluid leaks at a drape using sensing techniques |
US8676338B2 (en) | 2010-07-20 | 2014-03-18 | Zeltiq Aesthetics, Inc. | Combined modality treatment systems, methods and apparatus for body contouring applications |
DE202010012119U1 (en) * | 2010-09-01 | 2010-11-25 | Zisser Gmbh | Device for the cosmetic and / or medical treatment of the skin surface by ice and light |
KR101269970B1 (en) | 2010-11-15 | 2013-05-31 | 주식회사 루트로닉 | An optical apparatus for skin treatment and a method for controlling the optical apparatus |
US10722395B2 (en) | 2011-01-25 | 2020-07-28 | Zeltiq Aesthetics, Inc. | Devices, application systems and methods with localized heat flux zones for removing heat from subcutaneous lipid-rich cells |
EP2717775A4 (en) * | 2011-06-10 | 2014-11-26 | Dermalucent Llc | Tissue optical clearing devices for subsurface light-induced phase-change and methods of use |
EP2723210B1 (en) * | 2011-06-22 | 2018-05-02 | ICTV Brands, Inc. | Hair removal and re-growth suppression apparatus |
US9314301B2 (en) | 2011-08-01 | 2016-04-19 | Miramar Labs, Inc. | Applicator and tissue interface module for dermatological device |
US8771328B2 (en) | 2011-09-08 | 2014-07-08 | La Lumiere Llc | Light therapy platform system |
US10195458B2 (en) | 2011-09-08 | 2019-02-05 | Johnson & Johnson Consumer Inc. | Light therapy platform enhanced controller |
US10272257B2 (en) | 2011-09-08 | 2019-04-30 | Johnson & Johnson Consumer, Inc. | Light therapy platform inductive mask and charger |
US10434325B2 (en) | 2011-09-08 | 2019-10-08 | Johnson & Johnson Consumer Inc. | Light therapy platform mobile device applications |
US10092770B2 (en) | 2011-09-08 | 2018-10-09 | Johnson & Johnson Consumer Inc. | Light therapy spot applicator |
US10090694B2 (en) | 2011-09-08 | 2018-10-02 | Johnson & Johnson Consumer Inc. | Light therapy platform mobile phone charger |
US10022554B2 (en) | 2013-03-15 | 2018-07-17 | Johnson & Johnson Consumer Inc. | Light therapy bandage system |
US10213618B2 (en) | 2011-09-08 | 2019-02-26 | Johnson & Johnson Consumer, Inc. | Light therapy platform combination mask |
US9789333B2 (en) | 2011-09-08 | 2017-10-17 | Johnson & Johnson Consumer Inc. | Light therapy platform system |
US10709600B2 (en) | 2011-09-20 | 2020-07-14 | The Centre, P.C. | Stretch mark removal device |
WO2013046086A1 (en) * | 2011-09-26 | 2013-04-04 | Koninklijke Philips Electronics N.V. | Skin treatment device with radiation emission protection |
KR101322658B1 (en) * | 2011-11-24 | 2013-10-30 | 주식회사 루트로닉 | Apparatus for treating medical using laser |
US9780518B2 (en) | 2012-04-18 | 2017-10-03 | Cynosure, Inc. | Picosecond laser apparatus and methods for treating target tissues with same |
WO2013190537A1 (en) * | 2012-06-18 | 2013-12-27 | Michael Tavger | Method and system for delivering solution into the pores of recipient human skin |
US9993658B2 (en) | 2012-08-16 | 2018-06-12 | Yolo Medical Inc. | Light applicators, systems and methods |
USD903887S1 (en) | 2012-09-05 | 2020-12-01 | Johnson & Johnson Consumer Inc. | Handheld acne treatment wand |
US9844460B2 (en) | 2013-03-14 | 2017-12-19 | Zeltiq Aesthetics, Inc. | Treatment systems with fluid mixing systems and fluid-cooled applicators and methods of using the same |
US9545523B2 (en) | 2013-03-14 | 2017-01-17 | Zeltiq Aesthetics, Inc. | Multi-modality treatment systems, methods and apparatus for altering subcutaneous lipid-rich tissue |
WO2014145707A2 (en) | 2013-03-15 | 2014-09-18 | Cynosure, Inc. | Picosecond optical radiation systems and methods of use |
US10779885B2 (en) | 2013-07-24 | 2020-09-22 | Miradry. Inc. | Apparatus and methods for the treatment of tissue using microwave energy |
WO2015117032A1 (en) | 2014-01-31 | 2015-08-06 | Zeltiq Aesthestic, Inc. | Treatment systems for treating glands by cooling |
US10675176B1 (en) | 2014-03-19 | 2020-06-09 | Zeltiq Aesthetics, Inc. | Treatment systems, devices, and methods for cooling targeted tissue |
USD777338S1 (en) | 2014-03-20 | 2017-01-24 | Zeltiq Aesthetics, Inc. | Cryotherapy applicator for cooling tissue |
US10952891B1 (en) | 2014-05-13 | 2021-03-23 | Zeltiq Aesthetics, Inc. | Treatment systems with adjustable gap applicators and methods for cooling tissue |
USD762870S1 (en) | 2014-07-30 | 2016-08-02 | Vijay Singh | LED light therapy tape |
US10568759B2 (en) | 2014-08-19 | 2020-02-25 | Zeltiq Aesthetics, Inc. | Treatment systems, small volume applicators, and methods for treating submental tissue |
US10935174B2 (en) | 2014-08-19 | 2021-03-02 | Zeltiq Aesthetics, Inc. | Stress relief couplings for cryotherapy apparatuses |
US10179229B2 (en) | 2014-12-23 | 2019-01-15 | Edge Systems Llc | Devices and methods for treating the skin using a porous member |
EP3237055B1 (en) | 2014-12-23 | 2020-08-12 | Edge Systems LLC | Devices and methods for treating the skin using a rollerball or a wicking member |
US10737109B2 (en) | 2015-04-23 | 2020-08-11 | Cynosure, Llc | Systems and methods of unattended treatment of a subject's head or neck |
US10518104B2 (en) | 2015-04-23 | 2019-12-31 | Cynosure, Llc | Systems and methods of unattended treatment |
KR20240014104A (en) | 2015-07-08 | 2024-01-31 | 하이드라페이셜 엘엘씨 | Devices, systems and methods for promoting hair growth |
US20170050048A1 (en) * | 2015-08-10 | 2017-02-23 | Oren Aharon | Method or apparatus for wrinkle treatment |
WO2017070112A1 (en) | 2015-10-19 | 2017-04-27 | Zeltiq Aesthetics, Inc. | Vascular treatment systems, cooling devices, and methods for cooling vascular structures |
CN108472151B (en) | 2016-01-07 | 2020-10-27 | 斯尔替克美学股份有限公司 | Temperature-dependent adhesion between applicator and skin during tissue cooling |
US10765552B2 (en) | 2016-02-18 | 2020-09-08 | Zeltiq Aesthetics, Inc. | Cooling cup applicators with contoured heads and liner assemblies |
US10682297B2 (en) | 2016-05-10 | 2020-06-16 | Zeltiq Aesthetics, Inc. | Liposomes, emulsions, and methods for cryotherapy |
US11382790B2 (en) | 2016-05-10 | 2022-07-12 | Zeltiq Aesthetics, Inc. | Skin freezing systems for treating acne and skin conditions |
US10555831B2 (en) | 2016-05-10 | 2020-02-11 | Zeltiq Aesthetics, Inc. | Hydrogel substances and methods of cryotherapy |
BR112019010363A2 (en) | 2016-11-22 | 2019-08-27 | Dominion Aesthetic Tech Inc | systems and methods for aesthetic treatment |
US11076879B2 (en) | 2017-04-26 | 2021-08-03 | Zeltiq Aesthetics, Inc. | Shallow surface cryotherapy applicators and related technology |
US10632324B2 (en) | 2017-04-27 | 2020-04-28 | 9127-4910 Quebec Inc. | Method for the treatment of skin tissues |
IT201700117730A1 (en) * | 2017-10-18 | 2019-04-18 | El En Spa | LASER ENERGY APPLICATOR WITH COOLING SYSTEM, APPLIANCE AND METHOD USING THIS DEVICE |
US11400308B2 (en) | 2017-11-21 | 2022-08-02 | Cutera, Inc. | Dermatological picosecond laser treatment systems and methods using optical parametric oscillator |
WO2019165426A1 (en) | 2018-02-26 | 2019-08-29 | Cynosure, Inc. | Q-switched cavity dumped sub-nanosecond laser |
RU2770556C1 (en) * | 2018-06-08 | 2022-04-18 | Кванта Систем С.П.А. | System for photothermal targeted therapy with integrated pre-conditioning and automatic initiation of photothermal targeted therapy by measuring the skin surface temperature, and corresponding methods |
CA3107932A1 (en) | 2018-07-31 | 2020-02-06 | Zeltiq Aesthetics, Inc. | Methods, devices, and systems for improving skin characteristics |
CN113286555A (en) * | 2018-10-22 | 2021-08-20 | 艾库尔粉刺治疗公司 | Dosimetry determination process and predictive closed-loop control using skin surface temperature measurements and associated methods |
US10864380B1 (en) * | 2020-02-29 | 2020-12-15 | Cutera, Inc. | Systems and methods for controlling therapeutic laser pulse duration |
US11253720B2 (en) | 2020-02-29 | 2022-02-22 | Cutera, Inc. | Dermatological systems and methods with handpiece for coaxial pulse delivery and temperature sensing |
USD1016615S1 (en) | 2021-09-10 | 2024-03-05 | Hydrafacial Llc | Container for a skin treatment device |
WO2023223221A1 (en) * | 2022-05-19 | 2023-11-23 | El.En. S.P.A. | Handpiece for the treatment of skin by light radiation |
Family Cites Families (680)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US853033A (en) * | 1906-07-11 | 1907-05-07 | Harvey H Roberts | Portable electric-light cabinet. |
US1590283A (en) * | 1924-10-20 | 1926-06-29 | De Forest B Catlin | Therapeutic device |
BE346723A (en) * | 1926-11-13 | |||
US2472385A (en) * | 1946-07-18 | 1949-06-07 | Michael A Rollman | Massage device |
US2669771A (en) * | 1949-11-17 | 1954-02-23 | Gen Motors Corp | Armature coil lead staker |
US3327712A (en) | 1961-09-15 | 1967-06-27 | Ira H Kaufman | Photocoagulation type fiber optical surgical device |
US3261978A (en) * | 1963-05-27 | 1966-07-19 | Henry S Brenman | Dental cleaning apparatus |
US3538919A (en) | 1967-04-07 | 1970-11-10 | Gregory System Inc | Depilation by means of laser energy |
US3527932A (en) | 1967-11-16 | 1970-09-08 | James J Thomas | Transilluminating flashlight |
US3486070A (en) * | 1968-04-29 | 1969-12-23 | Westinghouse Electric Corp | Solid-state constant power ballast for electric discharge device |
US3597652A (en) * | 1969-01-14 | 1971-08-03 | Eg & G Inc | Apparatus for maintaining the temperature and operating a calibrated lamp in a constant resistance mode |
US3622743A (en) | 1969-04-28 | 1971-11-23 | Hrand M Muncheryan | Laser eraser and microwelder |
US4456872A (en) * | 1969-10-27 | 1984-06-26 | Bose Corporation | Current controlled two-state modulation |
US3653778A (en) * | 1970-04-16 | 1972-04-04 | John Robert Freiling | Applicator device for toothpaste dispensers or the like |
US3667454A (en) * | 1970-06-12 | 1972-06-06 | Larry W Prince | Toothbrush with ultraviolet emitter |
US3693623A (en) | 1970-12-25 | 1972-09-26 | Gregory System Inc | Photocoagulation means and method for depilation |
US3793723A (en) * | 1971-12-03 | 1974-02-26 | Ultrasonic Systems | Ultrasonic replaceable shaving head and razor |
US3846811A (en) * | 1972-03-29 | 1974-11-05 | Canon Kk | Flash unit for use with camera |
US3818914A (en) * | 1972-04-17 | 1974-06-25 | Spectroderm Inc | Apparatus and method for treatment of skin disorders |
FR2199453B1 (en) | 1972-05-12 | 1974-10-25 | Busser Francis | |
US3857015A (en) * | 1972-11-08 | 1974-12-24 | O Richardson | Electrically heated heat sealing implement |
US3834391A (en) | 1973-01-19 | 1974-09-10 | Block Carol Ltd | Method and apparatus for photoepilation |
GB1458356A (en) * | 1973-01-31 | 1976-12-15 | Wilkinson Sword Ltd | Shaving equipment |
US3909649A (en) * | 1973-04-05 | 1975-09-30 | Gen Electric | Electric lamp with light-diffusing coating |
US3890537A (en) * | 1974-01-02 | 1975-06-17 | Gen Electric | Solid state chopper ballast for gaseous discharge lamps |
US3977083A (en) * | 1974-02-05 | 1976-08-31 | Norman Leslie | Dental instrument |
US3900034A (en) | 1974-04-10 | 1975-08-19 | Us Energy | Photochemical stimulation of nerves |
GB1485908A (en) | 1974-05-21 | 1977-09-14 | Nath G | Apparatus for applying light radiation |
CA1086172A (en) | 1975-03-14 | 1980-09-23 | Robert F. Shaw | Surgical instrument having self-regulating radiant heating of its cutting edge and method of using the same |
DE2609273A1 (en) * | 1976-03-05 | 1977-09-08 | Mutzhas Maximilian F | IRRADIATION DEVICE WITH ULTRAVIOLET RADIATION SOURCE |
US4047106A (en) * | 1976-06-01 | 1977-09-06 | Charles Elbert Robinson | Motor speed sensor |
US4273109A (en) * | 1976-07-06 | 1981-06-16 | Cavitron Corporation | Fiber optic light delivery apparatus and medical instrument utilizing same |
JPS6043134B2 (en) * | 1977-08-25 | 1985-09-26 | 信紘 佐藤 | Device for measuring reflection characteristics of biological organs and tissues |
US4294263A (en) | 1977-12-07 | 1981-10-13 | Air Shields, Inc. | System for detecting probe dislodgement |
DE7906381U1 (en) | 1979-03-08 | 1979-07-12 | Richard Wolf Gmbh, 7134 Knittlingen | LIGHTING FOR OPERATIONAL AND EXAMINATION AREAS |
JPS55129327A (en) * | 1979-03-28 | 1980-10-07 | Minolta Camera Co Ltd | Constant intensity light emitting strobe device |
US4269067A (en) * | 1979-05-18 | 1981-05-26 | International Business Machines Corporation | Method and apparatus for focusing elastic waves converted from thermal energy |
FR2465213A1 (en) | 1979-09-13 | 1981-03-20 | Oreal | APPARATUS FOR DIGITAL COLORING OR COLOR MODIFICATION OF AN OBJECT |
JPS56156150A (en) | 1980-02-27 | 1981-12-02 | Nato Giyuntaa | Photocoagulator |
US4333197A (en) * | 1980-06-02 | 1982-06-08 | Arthur Kuris | Ultrasonic toothbrush |
US4316467A (en) | 1980-06-23 | 1982-02-23 | Lorenzo P. Maun | Control for laser hemangioma treatment system |
US4335726A (en) * | 1980-07-11 | 1982-06-22 | The Kendall Company | Therapeutic device with temperature and pressure control |
FR2498927A1 (en) * | 1981-02-05 | 1982-08-06 | Javelle Edmond | APPARATUS FOR HANDLING THE ENERGY CIRCULATING IN THE MERIDIENS OF THE HUMAN BODY |
US4388924A (en) | 1981-05-21 | 1983-06-21 | Weissman Howard R | Method for laser depilation |
JPS5886178A (en) * | 1981-11-18 | 1983-05-23 | 松下電器産業株式会社 | Laser medical apparatus |
US4409479A (en) * | 1981-12-03 | 1983-10-11 | Xerox Corporation | Optical cursor control device |
US4461294A (en) | 1982-01-20 | 1984-07-24 | Baron Neville A | Apparatus and process for recurving the cornea of an eye |
GB2123287B (en) | 1982-07-09 | 1986-03-05 | Anna Gunilla Sutton | Depilaton device |
US5928222A (en) | 1982-08-06 | 1999-07-27 | Kleinerman; Marcos Y. | Fiber optic sensing techniques in laser medicine |
AU553836B2 (en) | 1982-08-27 | 1986-07-31 | Alistair Joseph Blake | Lamp for irradiating tumours |
US4452081A (en) * | 1982-09-30 | 1984-06-05 | Varian Associates, Inc. | Measurement of velocity and tissue temperature by ultrasound |
US4566271A (en) * | 1982-12-01 | 1986-01-28 | Lucas Industries Public Limited Company | Engine systems |
US4784135A (en) * | 1982-12-09 | 1988-11-15 | International Business Machines Corporation | Far ultraviolet surgical and dental procedures |
US4504727A (en) * | 1982-12-30 | 1985-03-12 | International Business Machines Corporation | Laser drilling system utilizing photoacoustic feedback |
DE3304230A1 (en) | 1983-02-08 | 1984-08-16 | ams Automatische Meß- und Steuerungstechnik GmbH, 8572 Auerbach | RADIATION DEVICE |
US5527368C1 (en) | 1983-03-11 | 2001-05-08 | Norton Co | Coated abrasives with rapidly curable adhesives |
US4524289A (en) * | 1983-04-11 | 1985-06-18 | Xerox Corporation | Flash lamp power supply with reduced capacitance requirements |
US4601753A (en) * | 1983-05-05 | 1986-07-22 | General Electric Company | Powdered iron core magnetic devices |
US4591762A (en) * | 1983-05-31 | 1986-05-27 | Olympus Optical, Co. | Electronic flash |
GB8320639D0 (en) * | 1983-07-30 | 1983-09-01 | Emi Plc Thorn | Incandescent lamps |
JPS60123818A (en) | 1983-12-08 | 1985-07-02 | Olympus Optical Co Ltd | Optical transmitter |
US4512197A (en) * | 1983-09-01 | 1985-04-23 | The United States Of America As Represented By The Secretary Of The Navy | Apparatus for generating a focusable and scannable ultrasonic beam for non-destructive examination |
US4608978A (en) | 1983-09-26 | 1986-09-02 | Carol Block Limited | Method and apparatus for photoepiltion |
US5140984A (en) | 1983-10-06 | 1992-08-25 | Proclosure, Inc. | Laser healing method and apparatus |
US5108388B1 (en) | 1983-12-15 | 2000-09-19 | Visx Inc | Laser surgery method |
JPS60148567A (en) | 1984-01-13 | 1985-08-05 | 株式会社東芝 | Laser treatment apparatus |
JPS60148566A (en) * | 1984-01-13 | 1985-08-05 | 株式会社東芝 | Laser treatment apparatus |
US4608979A (en) * | 1984-02-22 | 1986-09-02 | Washington Research Foundation | Apparatus for the noninvasive shock fragmentation of renal calculi |
IL75998A0 (en) | 1984-08-07 | 1985-12-31 | Medical Laser Research & Dev C | Laser system for providing target tissue specific energy deposition |
US4799479A (en) * | 1984-10-24 | 1989-01-24 | The Beth Israel Hospital Association | Method and apparatus for angioplasty |
US4677347A (en) * | 1984-10-26 | 1987-06-30 | Olympus Optical, Co., Ltd. | Electronic flash |
US5192278A (en) | 1985-03-22 | 1993-03-09 | Massachusetts Institute Of Technology | Multi-fiber plug for a laser catheter |
US5318024A (en) | 1985-03-22 | 1994-06-07 | Massachusetts Institute Of Technology | Laser endoscope for spectroscopic imaging |
DE3666773D1 (en) | 1985-03-29 | 1989-12-14 | Eugene Jim Politzer | Method and apparatus for shaving the beard |
SU1257475A1 (en) | 1985-04-09 | 1986-09-15 | Ленинградский Ордена Трудового Красного Знамени Институт Точной Механики И Оптики | Laser interferometric device for determining non-linearity refractive index of optical media |
US4623929A (en) * | 1985-05-03 | 1986-11-18 | Eastman Kodak Company | Flash tube simmer circuitry for a film video player electronic strobe light |
US4917084A (en) | 1985-07-31 | 1990-04-17 | C. R. Bard, Inc. | Infrared laser catheter system |
US5196004A (en) | 1985-07-31 | 1993-03-23 | C. R. Bard, Inc. | Infrared laser catheter system |
EP0214712B1 (en) | 1985-07-31 | 1992-09-02 | C.R. Bard, Inc. | Infrared laser catheter apparatus |
US5137530A (en) | 1985-09-27 | 1992-08-11 | Sand Bruce J | Collagen treatment apparatus |
GB2184021A (en) | 1985-12-13 | 1987-06-17 | Micra Ltd | Laser treatment apparatus for port wine stains |
US4695697A (en) * | 1985-12-13 | 1987-09-22 | Gv Medical, Inc. | Fiber tip monitoring and protection assembly |
FR2591902B1 (en) | 1985-12-23 | 1989-06-30 | Collin Yvon | EXTERNAL LASER THERAPY APPARATUS HAVING ONE OR MORE LASER DIODES IN SUCTION CUPS |
US4871479A (en) * | 1986-03-25 | 1989-10-03 | Comurhex Societe Pour La Conversion De L'uranium En Metal Et Hexafluorure | Process for producing sintered mixed oxides which are soluble in nitric acid from solutions of nitrates |
SU1326962A1 (en) | 1986-03-31 | 1987-07-30 | Ленинградский Институт Точной Механики И Оптики | Method of determining nonlinearity of refractive index of optical media |
US4775361A (en) * | 1986-04-10 | 1988-10-04 | The General Hospital Corporation | Controlled removal of human stratum corneum by pulsed laser to enhance percutaneous transport |
US5336217A (en) | 1986-04-24 | 1994-08-09 | Institut National De La Sante Et De La Recherche Medicale (Insepm) | Process for treatment by irradiating an area of a body, and treatment apparatus usable in dermatology for the treatment of cutaneous angio dysplasias |
FR2597744A1 (en) | 1986-04-29 | 1987-10-30 | Boussignac Georges | CARDIO-VASCULAR CATHETER FOR LASER SHOOTING |
JPS6397175A (en) * | 1986-10-15 | 1988-04-27 | 森 敬 | Light irradiation apparatus for emitting tooth germ treating light |
US4826431A (en) * | 1986-06-12 | 1989-05-02 | Kabushiki Kaisha Morita Seisakusho | Medical laser handpiece |
US4736745A (en) * | 1986-06-27 | 1988-04-12 | University Of Cincinnati | Laser treatment of cancerization of the oral cavity and apparatus for use therewith |
EP0272325A1 (en) | 1986-06-30 | 1988-06-29 | MEDICAL LASER RESEARCH Co., LTD. | Semiconductor laser therapeutic apparatus |
US4926227A (en) | 1986-08-01 | 1990-05-15 | Nanometrics Inc. | Sensor devices with internal packaged coolers |
US4779173A (en) * | 1986-12-24 | 1988-10-18 | Carr Charlie O | Illuminated brush device |
US4840563A (en) * | 1987-02-26 | 1989-06-20 | Siemens Aktiengesellschaft | Dental equipment having means for delivering RF and LF energy to a dental handpiece |
JPS63216579A (en) * | 1987-03-05 | 1988-09-08 | 大工園 則雄 | Laser beam irradiation apparatus for hyperthermia |
DE8705296U1 (en) * | 1987-04-09 | 1988-08-04 | Heimann Gmbh, 6200 Wiesbaden, De | |
US4749913A (en) * | 1987-04-17 | 1988-06-07 | General Electric Company | Operating circuit for a direct current discharge lamp |
US4745909A (en) * | 1987-05-15 | 1988-05-24 | Pelton Robert J | Cold massage tool and method of use thereof |
JPH01178256A (en) | 1988-01-05 | 1989-07-14 | Hideo Suyama | Electronic toothbrush |
US4862903A (en) * | 1987-10-09 | 1989-09-05 | U.S. Divers Company, Inc. | Breathing mouthpiece for contacting upper palate and lower jaw of user's mouth |
JPH0199574A (en) | 1987-10-13 | 1989-04-18 | Matsushita Electric Ind Co Ltd | Medical equipment with semiconductor laser |
US4860744A (en) | 1987-11-02 | 1989-08-29 | Raj K. Anand | Thermoelectrically controlled heat medical catheter |
US4930504A (en) | 1987-11-13 | 1990-06-05 | Diamantopoulos Costas A | Device for biostimulation of tissue and method for treatment of tissue |
US4845608A (en) * | 1987-12-21 | 1989-07-04 | General Electric Company | Digital speed controller using a single-chip microcontroller |
US4860172A (en) | 1988-01-19 | 1989-08-22 | Biotronics Associates, Inc. | Lamp-based laser simulator |
JP2708191B2 (en) | 1988-09-20 | 1998-02-04 | 株式会社日立製作所 | Semiconductor device |
US5242437A (en) | 1988-06-10 | 1993-09-07 | Trimedyne Laser Systems, Inc. | Medical device applying localized high intensity light and heat, particularly for destruction of the endometrium |
JPH0213479A (en) * | 1988-07-01 | 1990-01-17 | Takashi Mori | Light radiation device for medical therapy |
US4884560A (en) | 1988-07-11 | 1989-12-05 | Kuracina Thomas C | Thermal massage device |
GB8816648D0 (en) * | 1988-07-13 | 1988-08-17 | Rowland A C | Light delivery system |
US4928038A (en) | 1988-09-26 | 1990-05-22 | General Electric Company | Power control circuit for discharge lamp and method of operating same |
DE3837248A1 (en) | 1988-10-28 | 1990-05-03 | Teichmann Heinrich Otto Dr Phy | Device for treating skin lesions |
JP2592791B2 (en) | 1989-01-31 | 1997-03-19 | 株式会社サンギ | Electronic toothbrush |
US4945239A (en) | 1989-03-29 | 1990-07-31 | Center For Innovative Technology | Early detection of breast cancer using transillumination |
US5263951A (en) | 1989-04-21 | 1993-11-23 | Kerus Medical Systems | Correction of the optical focusing system of the eye using laser thermal keratoplasty |
CN2053926U (en) | 1989-05-06 | 1990-03-07 | 李杰生 | Radiation treatment apparatus |
US5057104A (en) | 1989-05-30 | 1991-10-15 | Cyrus Chess | Method and apparatus for treating cutaneous vascular lesions |
US5486172A (en) | 1989-05-30 | 1996-01-23 | Chess; Cyrus | Apparatus for treating cutaneous vascular lesions |
US5152759A (en) | 1989-06-07 | 1992-10-06 | University Of Miami, School Of Medicine, Dept. Of Ophthalmology | Noncontact laser microsurgical apparatus |
US4973848A (en) * | 1989-07-28 | 1990-11-27 | J. Mccaughan | Laser apparatus for concurrent analysis and treatment |
US5955490A (en) | 1989-07-28 | 1999-09-21 | Queen's University At Kingston | Photochemotherapeutic method using 5-aminolevulinic acid and other precursors of endogenous porphyrins |
JP2854027B2 (en) | 1989-08-03 | 1999-02-03 | ヤーマン株式会社 | Light hair removal device |
JPH0373106A (en) * | 1989-08-14 | 1991-03-28 | Omron Corp | Optical medical toothbrush |
WO1991002562A1 (en) | 1989-08-17 | 1991-03-07 | Surgical Laser Products, Inc. | Integral end structure for medical laser waveguide |
US5182557A (en) | 1989-09-20 | 1993-01-26 | Semborg Recrob, Corp. | Motorized joystick |
US4992256A (en) * | 1989-09-27 | 1991-02-12 | Colgate-Palmolive Company | Plaque disclosing compositions |
DE3936367A1 (en) | 1989-11-02 | 1991-05-08 | Simon Pal | SHAVER |
US4979180A (en) * | 1989-11-24 | 1990-12-18 | Muncheryan Arthur M | Modular interchangeable laser system |
GB2239675A (en) | 1989-12-05 | 1991-07-10 | Man Fai Shiu | Pump for pumping liquid |
FR2655849B1 (en) | 1989-12-19 | 1997-10-31 | Raymond Bontemps | LOCAL CRYOGENIC DEVICE FOR MASSAGE OF THE SKIN. |
US5032178A (en) * | 1990-02-02 | 1991-07-16 | Demetron Research Corporation | Dental composition system and method for bleaching teeth |
US4976308A (en) * | 1990-02-21 | 1990-12-11 | Wright State University | Thermal energy storage heat exchanger |
SE465953B (en) | 1990-04-09 | 1991-11-25 | Morgan Gustafsson | DEVICE FOR TREATMENT OF UNDESECTED EXTERNAL ACCOMMODATIONS |
US5059192A (en) | 1990-04-24 | 1991-10-22 | Nardo Zaias | Method of hair depilation |
US5725522A (en) | 1990-06-15 | 1998-03-10 | Rare Earth Medical, Inc. | Laser suturing of biological materials |
US5071417A (en) | 1990-06-15 | 1991-12-10 | Rare Earth Medical Lasers, Inc. | Laser fusion of biological materials |
AU642266B2 (en) | 1990-06-25 | 1993-10-14 | Kevin John Bourke | Method and apparatus for dental treatment |
US5046494A (en) * | 1990-08-27 | 1991-09-10 | John Searfoss | Phototherapy method |
DE4032860A1 (en) | 1990-10-12 | 1992-04-16 | Zeiss Carl Fa | POWER-CONTROLLED CONTACT APPLICATOR FOR LASER RADIATION |
US5549660A (en) | 1990-11-15 | 1996-08-27 | Amron, Ltd. | Method of treating acne |
DE4100442C2 (en) | 1991-01-09 | 1994-02-10 | Texas Instruments Deutschland | Arrangement for monitoring operating parameters of pneumatic tires of a vehicle mounted on wheel rims |
US5065515A (en) | 1991-01-24 | 1991-11-19 | Warner-Lambert Company | Thermally assisted shaving system |
US5300097A (en) | 1991-02-13 | 1994-04-05 | Lerner Ethan A | Fiber optic psoriasis treatment device |
DE9102407U1 (en) | 1991-02-28 | 1991-07-11 | Mink, Mathias, 7570 Baden-Baden, De | |
US5369831A (en) | 1991-03-25 | 1994-12-06 | Sonex International Corporation | Therapeutic ultrasonic toothbrush |
US5207671A (en) | 1991-04-02 | 1993-05-04 | Franken Peter A | Laser debridement of wounds |
US6485413B1 (en) | 1991-04-29 | 2002-11-26 | The General Hospital Corporation | Methods and apparatus for forward-directed optical scanning instruments |
RU2122848C1 (en) | 1991-06-24 | 1998-12-10 | Учебно-научно-производственный лазерный центр Санкт-Петербургского института точной механики и оптики | Reflexotherapy device |
US5474549A (en) | 1991-07-09 | 1995-12-12 | Laserscope | Method and system for scanning a laser beam for controlled distribution of laser dosage |
US5178617A (en) | 1991-07-09 | 1993-01-12 | Laserscope | System for controlled distribution of laser dosage |
US5159601A (en) | 1991-07-17 | 1992-10-27 | General Instrument Corporation | Method for producing a tunable erbium fiber laser |
JP2754964B2 (en) | 1991-08-13 | 1998-05-20 | 日本電気株式会社 | Multi-pole connector mating structure |
US5225926A (en) | 1991-09-04 | 1993-07-06 | International Business Machines Corporation | Durable optical elements fabricated from free standing polycrystalline diamond and non-hydrogenated amorphous diamond like carbon (dlc) thin films |
US5267399A (en) | 1991-09-09 | 1993-12-07 | Johnston William A | Implement for simultaneous skin chilling and chilled gel application |
US5171564A (en) | 1991-09-13 | 1992-12-15 | Colgate-Palmolive | Aqueous tooth whitening dentifrice |
US5370642A (en) * | 1991-09-25 | 1994-12-06 | Keller; Gregory S. | Method of laser cosmetic surgery |
US5293880A (en) | 1991-10-02 | 1994-03-15 | Levitt Steven J | Athletic mouthguard |
US6461296B1 (en) | 1998-06-26 | 2002-10-08 | 2000 Injectx, Inc. | Method and apparatus for delivery of genes, enzymes and biological agents to tissue cells |
US5226907A (en) | 1991-10-29 | 1993-07-13 | Tankovich Nikolai I | Hair removal device and method |
US5817089A (en) * | 1991-10-29 | 1998-10-06 | Thermolase Corporation | Skin treatment process using laser |
US5425728A (en) | 1991-10-29 | 1995-06-20 | Tankovich; Nicolai I. | Hair removal device and method |
US5871480A (en) | 1991-10-29 | 1999-02-16 | Thermolase Corporation | Hair removal using photosensitizer and laser |
US5303585A (en) | 1991-10-31 | 1994-04-19 | Jtl Medical Corporation | Fluid volume sensor |
US5344418A (en) | 1991-12-12 | 1994-09-06 | Shahriar Ghaffari | Optical system for treatment of vascular lesions |
US5275596A (en) | 1991-12-23 | 1994-01-04 | Laser Centers Of America | Laser energy delivery tip element with throughflow of vaporized materials |
IL100545A (en) | 1991-12-29 | 1995-03-15 | Dimotech Ltd | Apparatus for photodynamic therapy treatment |
US5501680A (en) | 1992-01-15 | 1996-03-26 | The University Of Pittsburgh | Boundary and proximity sensor apparatus for a laser |
US5353790A (en) | 1992-01-17 | 1994-10-11 | Board Of Regents, The University Of Texas System | Method and apparatus for optical measurement of bilirubin in tissue |
US5160194A (en) | 1992-02-27 | 1992-11-03 | Feldman Melvin D | Toothbrush with externally illuminated bristles |
GB2270159A (en) | 1992-03-13 | 1994-03-02 | Scient Generics Ltd | Optically controlled ultrasound array |
WO1993018715A1 (en) | 1992-03-20 | 1993-09-30 | The General Hospital Corporation | Laser illuminator |
DE9204621U1 (en) | 1992-04-03 | 1992-07-30 | Oralia Dentalprodukte Gmbh, 7750 Konstanz, De | |
US5405368A (en) | 1992-10-20 | 1995-04-11 | Esc Inc. | Method and apparatus for therapeutic electromagnetic treatment |
CA2093055C (en) | 1992-04-09 | 2002-02-19 | Shimon Eckhouse | Method and apparatus for therapeutic electromagnetic treatment |
US5287372A (en) | 1992-04-24 | 1994-02-15 | Hughes Aircraft Company | Quasi-resonant diode drive current source |
US5334191A (en) | 1992-05-21 | 1994-08-02 | Dix Phillip Poppas | Laser tissue welding control system |
US5292320A (en) | 1992-07-06 | 1994-03-08 | Ceramoptec, Inc. | Radial medical laser delivery device |
EP0920840A3 (en) | 1992-07-31 | 2000-03-29 | Molten Corporation | Small-sized light irradiator for dental use |
US5596619A (en) | 1992-08-21 | 1997-01-21 | Nomos Corporation | Method and apparatus for conformal radiation therapy |
DE69311478T2 (en) | 1992-09-07 | 1998-01-02 | Philips Electronics Nv | Method for producing a block-shaped carrier body for a semiconductor component |
DE4232915A1 (en) | 1992-10-01 | 1994-04-07 | Hohla Kristian | Device for shaping the cornea by removing tissue |
US5306143A (en) | 1992-10-15 | 1994-04-26 | Laser Medical Technology, Inc. | Dental hygiene appliance |
US5720772A (en) | 1992-10-20 | 1998-02-24 | Esc Medical Systems Ltd. | 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 |
US5683380A (en) | 1995-03-29 | 1997-11-04 | Esc Medical Systems Ltd. | Method and apparatus for depilation using pulsed electromagnetic radiation |
US6280438B1 (en) | 1992-10-20 | 2001-08-28 | Esc Medical Systems Ltd. | Method and apparatus for electromagnetic treatment of the skin, including hair depilation |
US5626631A (en) | 1992-10-20 | 1997-05-06 | Esc Medical Systems Ltd. | Method and apparatus for therapeutic electromagnetic treatment |
GB2272278B (en) | 1992-10-23 | 1997-04-09 | Cancer Res Campaign Tech | Light source |
WO1995022283A1 (en) | 1992-10-26 | 1995-08-24 | Ultrasonic Sensing & Monitoring Systems, Inc. | Catheter using optical fibers to transmit laser and ultrasonic energy |
WO1994009694A1 (en) | 1992-10-28 | 1994-05-11 | Arsenault, Dennis, J. | Electronic endoscope |
US5334193A (en) | 1992-11-13 | 1994-08-02 | American Cardiac Ablation Co., Inc. | Fluid cooled ablation catheter |
US5342358A (en) | 1993-01-12 | 1994-08-30 | S.L.T. Japan Co., Ltd. | Apparatus for operation by laser energy |
US5287380A (en) | 1993-02-19 | 1994-02-15 | Candela Laser Corporation | Method and apparatus for generating long output pulses from flashlamp-excited lasers |
US5707403A (en) | 1993-02-24 | 1998-01-13 | Star Medical Technologies, Inc. | Method for the laser treatment of subsurface blood vessels |
DE9303352U1 (en) | 1993-03-08 | 1993-07-22 | Elfo Ag Sachseln, Sachseln, Ch | |
US5304170A (en) * | 1993-03-12 | 1994-04-19 | Green Howard A | Method of laser-induced tissue necrosis in carotenoid-containing skin structures |
US5350376A (en) | 1993-04-16 | 1994-09-27 | Ceramoptec, Inc. | Optical controller device |
GB9309397D0 (en) | 1993-05-07 | 1993-06-23 | Patel Bipin C M | Laser treatment |
US5454807A (en) | 1993-05-14 | 1995-10-03 | Boston Scientific Corporation | Medical treatment of deeply seated tissue using optical radiation |
US5403306A (en) * | 1993-06-22 | 1995-04-04 | Vanderbilt University | Laser surgery method |
US5860967A (en) | 1993-07-21 | 1999-01-19 | Lucid, Inc. | Dermatological laser treatment system with electronic visualization of the area being treated |
US5445608A (en) | 1993-08-16 | 1995-08-29 | James C. Chen | Method and apparatus for providing light-activated therapy |
US5420768A (en) | 1993-09-13 | 1995-05-30 | Kennedy; John | Portable led photocuring device |
US6251100B1 (en) | 1993-09-24 | 2001-06-26 | Transmedica International, Inc. | Laser assisted topical anesthetic permeation |
US6635075B2 (en) | 1993-10-04 | 2003-10-21 | Huan-Chen Li | Method and apparatus for treatment of skin itch and disease |
US6245093B1 (en) | 1993-10-04 | 2001-06-12 | Huan-Chen Li | Method and apparatus for treatment of skin itch and disease |
US5415654A (en) | 1993-10-05 | 1995-05-16 | S.L.T. Japan Co., Ltd. | Laser balloon catheter apparatus |
US5445611A (en) | 1993-12-08 | 1995-08-29 | Non-Invasive Monitoring Company (Nimco) | Enhancement of transdermal delivery with ultrasound and chemical enhancers |
US5885211A (en) * | 1993-11-15 | 1999-03-23 | Spectrix, Inc. | Microporation of human skin for monitoring the concentration of an analyte |
US5458140A (en) | 1993-11-15 | 1995-10-17 | Non-Invasive Monitoring Company (Nimco) | Enhancement of transdermal monitoring applications with ultrasound and chemical enhancers |
US5413587A (en) | 1993-11-22 | 1995-05-09 | Hochstein; Peter A. | Infrared heating apparatus and methods |
US20020019624A1 (en) | 1993-12-08 | 2002-02-14 | Clement Robert Marc | Depilation |
US5628744A (en) | 1993-12-21 | 1997-05-13 | Laserscope | Treatment beam handpiece |
WO1995017924A1 (en) | 1993-12-30 | 1995-07-06 | The General Hospital Corporation | Apparatus and methods for laser-induced superficial alteration of a substrate |
US5358503A (en) | 1994-01-25 | 1994-10-25 | Bertwell Dale E | Photo-thermal therapeutic device and method |
US5386427A (en) | 1994-02-10 | 1995-01-31 | Massachusetts Institute Of Technology | Thermally controlled lenses for lasers |
AT400305B (en) * | 1994-03-07 | 1995-12-27 | Divida Ges M B H Methoden Und | Instrument for the treatment of skin zones |
IL108918A (en) | 1994-03-10 | 1997-04-15 | Medic Lightech Ltd | Apparatus for efficient photodynamic treatment |
US5505726A (en) | 1994-03-21 | 1996-04-09 | Dusa Pharmaceuticals, Inc. | Article of manufacture for the photodynamic therapy of dermal lesion |
US5616140A (en) | 1994-03-21 | 1997-04-01 | Prescott; Marvin | Method and apparatus for therapeutic laser treatment |
US5561881A (en) | 1994-03-22 | 1996-10-08 | U.S. Philips Corporation | Electric toothbrush |
JP3530954B2 (en) * | 1994-03-24 | 2004-05-24 | 清之 竹迫 | Far-infrared sterilizer |
US5979454A (en) | 1995-05-15 | 1999-11-09 | The Regents Of The University Of California | Method and apparatus for causing rapid and deep spatially selective coagulation during thermally mediated therapeutic procedures |
JP3263275B2 (en) | 1994-04-05 | 2002-03-04 | ザ リージェンツ オブ ザ ユニバーシティ オブ カリフォルニア | Apparatus for laser treatment of living tissue and laser treatment apparatus for flame-like nevus |
RU2089126C1 (en) | 1994-04-11 | 1997-09-10 | Учебно-научно-производственный "Лазерный центр" Института точной механики и оптики | Method of treatment of tooth hard tissues by laser radiation and device for its realization |
AU2373695A (en) | 1994-05-03 | 1995-11-29 | Board Of Regents, The University Of Texas System | Apparatus and method for noninvasive doppler ultrasound-guided real-time control of tissue damage in thermal therapy |
FR2719470B1 (en) | 1994-05-04 | 1996-06-28 | Oreal | Method for bleaching hair by laser irradiation with cooling, and device for implementing it. |
US5519534A (en) | 1994-05-25 | 1996-05-21 | The Government Of The United States Of America As Represented By The Secretary Of The Department Of Health And Human Services | Irradiance attachment for an optical fiber to provide a uniform level of illumination across a plane |
US5652481A (en) | 1994-06-10 | 1997-07-29 | Beacon Light Products, Inc. | Automatic state tranition controller for a fluorescent lamp |
US5586132A (en) | 1994-07-27 | 1996-12-17 | Laser Industries Ltd. | Method and apparatus for generating bright light sources |
JPH0866781A (en) | 1994-08-30 | 1996-03-12 | Mitsubishi Electric Corp | Excimer laser beam irradiating device |
US5502582A (en) | 1994-09-02 | 1996-03-26 | Aavid Laboratories, Inc. | Light source cooler for LCD monitor |
US5531740A (en) | 1994-09-06 | 1996-07-02 | Rapistan Demag Corporation | Automatic color-activated scanning treatment of dermatological conditions by laser |
US5698866A (en) | 1994-09-19 | 1997-12-16 | Pdt Systems, Inc. | Uniform illuminator for phototherapy |
US5531739A (en) | 1994-09-23 | 1996-07-02 | Coherent, Inc. | Method of treating veins |
US5522813A (en) | 1994-09-23 | 1996-06-04 | Coherent, Inc. | Method of treating veins |
US5662643A (en) * | 1994-09-28 | 1997-09-02 | Abiomed R & D, Inc. | Laser welding system |
US5735884A (en) | 1994-10-04 | 1998-04-07 | Medtronic, Inc. | Filtered feedthrough assembly for implantable medical device |
US5746735A (en) | 1994-10-26 | 1998-05-05 | Cynosure, Inc. | Ultra long pulsed dye laser device for treatment of ectatic vessels and method therefor |
US5571098A (en) | 1994-11-01 | 1996-11-05 | The General Hospital Corporation | Laser surgical devices |
RU2089127C1 (en) | 1994-11-02 | 1997-09-10 | Григорий Борисович Альтшулер | Method of treatment of tooth hard tissues by laser radiation and device for its realization |
AT403654B (en) | 1994-12-01 | 1998-04-27 | Binder Michael Dr | DEVICE FOR THE OPTICAL EXAMINATION OF HUMAN SKIN AND THE SAME ASSIGNMENT EVALUATION DEVICE |
US5558667A (en) | 1994-12-14 | 1996-09-24 | Coherent, Inc. | Method and apparatus for treating vascular lesions |
AT401342B (en) | 1995-01-17 | 1996-08-26 | Myles Handels Gmbh | SOFTLASER WITH INTEGRATED POINT DETECTOR FOR ACUPUNCTURE POINTS |
US5743902A (en) | 1995-01-23 | 1998-04-28 | Coherent, Inc. | Hand-held laser scanner |
US5735844A (en) | 1995-02-01 | 1998-04-07 | The General Hospital Corporation | Hair removal using optical pulses |
US5595568A (en) | 1995-02-01 | 1997-01-21 | The General Hospital Corporation | Permanent hair removal using optical pulses |
US5643334A (en) | 1995-02-07 | 1997-07-01 | Esc Medical Systems Ltd. | Method and apparatus for the diagnostic and composite pulsed heating and photodynamic therapy treatment |
US5728090A (en) | 1995-02-09 | 1998-03-17 | Quantum Devices, Inc. | Apparatus for irradiating living cells |
RU2096051C1 (en) | 1995-02-24 | 1997-11-20 | Григорий Борисович Альтшулер | Apparatus for laser treatment of biological tissues (alternative embodiments) |
US5868731A (en) | 1996-03-04 | 1999-02-09 | Innotech Usa, Inc. | Laser surgical device and method of its use |
WO1996028212A1 (en) | 1995-03-09 | 1996-09-19 | Innotech Usa, Inc. | Laser surgical device and method of its use |
US5885273A (en) | 1995-03-29 | 1999-03-23 | Esc Medical Systems, Ltd. | Method for depilation using pulsed electromagnetic radiation |
RU2082337C1 (en) | 1995-04-10 | 1997-06-27 | Григорий Борисович Альтшулер | Tip piece of laser system for treating biological tissue |
US5658148A (en) | 1995-04-26 | 1997-08-19 | Ceramoptec Industries, Inc. | Dental laser brushing or cleaning device |
US6056548A (en) | 1995-04-26 | 2000-05-02 | Ceramoptec Industries, Inc. | Hygienic dental laser photo treatment method |
JPH08299310A (en) | 1995-05-02 | 1996-11-19 | Toa Medical Electronics Co Ltd | Non-invasive blood analysis device and method therefor |
US6425912B1 (en) | 1995-05-05 | 2002-07-30 | Thermage, Inc. | Method and apparatus for modifying skin surface and soft tissue structure |
US5660836A (en) | 1995-05-05 | 1997-08-26 | Knowlton; Edward W. | Method and apparatus for controlled contraction of collagen tissue |
US6241753B1 (en) | 1995-05-05 | 2001-06-05 | Thermage, Inc. | Method for scar collagen formation and contraction |
US6430446B1 (en) | 1995-05-05 | 2002-08-06 | Thermage, Inc. | Apparatus for tissue remodeling |
DE29508077U1 (en) | 1995-05-16 | 1995-08-10 | Wilden Lutz Dr Med | Oral care device |
US5673451A (en) | 1995-07-06 | 1997-10-07 | Moore; James R. | Instructional toothbrush |
US5658323A (en) | 1995-07-12 | 1997-08-19 | Miller; Iain D. | Method and apparatus for dermatology treatment |
US5879376A (en) | 1995-07-12 | 1999-03-09 | Luxar Corporation | Method and apparatus for dermatology treatment |
US6263233B1 (en) | 1995-07-13 | 2001-07-17 | Lucid, Inc. | Handheld imaging microscope |
US6240306B1 (en) | 1995-08-09 | 2001-05-29 | Rio Grande Medical Technologies, Inc. | Method and apparatus for non-invasive blood analyte measurement with fluid compartment equilibration |
US5849029A (en) | 1995-12-26 | 1998-12-15 | Esc Medical Systems, Ltd. | Method for controlling the thermal profile of the skin |
US5964749A (en) | 1995-09-15 | 1999-10-12 | Esc Medical Systems Ltd. | Method and apparatus for skin rejuvenation and wrinkle smoothing |
JPH0984803A (en) | 1995-09-27 | 1997-03-31 | Terumo Corp | Laser treatment apparatus |
US5836999A (en) | 1995-09-28 | 1998-11-17 | Esc Medical Systems Ltd. | Method and apparatus for treating psoriasis using pulsed electromagnetic radiation |
US5776175A (en) | 1995-09-29 | 1998-07-07 | Esc Medical Systems Ltd. | Method and apparatus for treatment of cancer using pulsed electromagnetic radiation |
US5824023A (en) | 1995-10-12 | 1998-10-20 | The General Hospital Corporation | Radiation-delivery device |
US5916211A (en) | 1995-11-03 | 1999-06-29 | Quon; Hew W. | Permanent hair removal using visible red wavelength spectrum lasers |
US5713738A (en) | 1995-12-12 | 1998-02-03 | Britesmile, Inc. | Method for whitening teeth |
US5879346A (en) | 1995-12-18 | 1999-03-09 | Esc Medical Systems, Ltd. | Hair removal by selective photothermolysis with an alexandrite laser |
CA2166034A1 (en) | 1995-12-22 | 1997-06-23 | Chia-Yu Cheng | Skin brush massage method |
KR0155936B1 (en) | 1995-12-26 | 1998-12-15 | 손욱 | Fluorescent lamp ballast circuit |
US6350276B1 (en) | 1996-01-05 | 2002-02-26 | Thermage, Inc. | Tissue remodeling apparatus containing cooling fluid |
IT1286551B1 (en) | 1996-02-13 | 1998-07-15 | El En S R L | DEVICE AND METHOD FOR THE ELIMINATION OF ADIPOSE LAYERS THROUGH LASER ENERGY |
US20070185552A1 (en) | 1996-02-13 | 2007-08-09 | Leonardo Masotti | Device and method for biological tissue stimulation by high intensity laser therapy |
US5835648A (en) | 1996-03-07 | 1998-11-10 | Miravant Systems, Inc. | Surface illuminator for photodynamic therapy |
US6239442B1 (en) | 1996-03-21 | 2001-05-29 | Keiji Iimura | Cleaning apparatus using ultraviolet rays |
JP3662068B2 (en) | 1996-03-21 | 2005-06-22 | 飯村 惠次 | Photocatalyst device and cleaning device using photocatalyst |
US5630811A (en) | 1996-03-25 | 1997-05-20 | Miller; Iain D. | Method and apparatus for hair removal |
AU2607197A (en) | 1996-04-09 | 1997-10-29 | Cynosure Corporation | Alexandrite laser system for treatment of dermatological specimens |
US5742392A (en) | 1996-04-16 | 1998-04-21 | Seymour Light, Inc. | Polarized material inspection apparatus |
US5944687A (en) | 1996-04-24 | 1999-08-31 | The Regents Of The University Of California | Opto-acoustic transducer for medical applications |
US5893828A (en) | 1996-05-02 | 1999-04-13 | Uram; Martin | Contact laser surgical endoscope and associated myringotomy procedure |
TW364841B (en) | 1996-05-14 | 1999-07-21 | Kao Corp | Toothbrush |
US5662644A (en) | 1996-05-14 | 1997-09-02 | Mdlt, Inc. | Dermatological laser apparatus and method |
US5655547A (en) * | 1996-05-15 | 1997-08-12 | Esc Medical Systems Ltd. | Method for laser surgery |
US5743901A (en) | 1996-05-15 | 1998-04-28 | Star Medical Technologies, Inc. | High fluence diode laser device and method for the fabrication and use thereof |
GB9611170D0 (en) | 1996-05-29 | 1996-07-31 | Sls Wales Ltd | Reduction of vascular blemishes by selective thermolysis |
US6183434B1 (en) | 1996-07-03 | 2001-02-06 | Spectrx, Inc. | Multiple mechanical microporation of skin or mucosa |
KR100205052B1 (en) | 1996-07-12 | 1999-06-15 | 정선종 | Mode locking optical fiber laser of wavelength tunable type |
WO1998004184A2 (en) | 1996-07-25 | 1998-02-05 | Light Medicine, Inc. | Photodynamic therapy apparatus and methods |
US6443974B1 (en) | 1996-07-28 | 2002-09-03 | Biosense, Inc. | Electromagnetic cardiac biostimulation |
US5814008A (en) | 1996-07-29 | 1998-09-29 | Light Sciences Limited Partnership | Method and device for applying hyperthermia to enhance drug perfusion and efficacy of subsequent light therapy |
US5820626A (en) * | 1996-07-30 | 1998-10-13 | Laser Aesthetics, Inc. | Cooling laser handpiece with refillable coolant reservoir |
AU3825097A (en) | 1996-08-06 | 1998-02-25 | Edward W. Knowlton | Method for tightening skin |
US5913883A (en) | 1996-08-06 | 1999-06-22 | Alexander; Dane | Therapeutic facial mask |
US6096029A (en) | 1997-02-24 | 2000-08-01 | Laser Skin Toner, Inc. | Laser method for subsurface cutaneous treatment |
NO963546D0 (en) | 1996-08-23 | 1996-08-23 | Eric Larsen | Method of permanent hair removal using light |
US5851181A (en) | 1996-08-30 | 1998-12-22 | Esc Medical Systems Ltd. | Apparatus for simultaneously viewing and spectrally analyzing a portion of skin |
AU3314297A (en) * | 1996-09-04 | 1998-03-12 | Esc Medical Systems Ltd. | Device and method for cooling skin during laser treatment |
US6214034B1 (en) | 1996-09-04 | 2001-04-10 | Radiancy, Inc. | Method of selective photothermolysis |
US5759200A (en) | 1996-09-04 | 1998-06-02 | Azar; Zion | Method of selective photothermolysis |
AU7101396A (en) | 1996-09-10 | 1998-04-02 | Grigory Borisovich Altshuler | Toothbrush |
US5908418A (en) | 1996-09-13 | 1999-06-01 | Dority; Douglas B. | Hand held coagulating device |
JP3036232U (en) * | 1996-09-26 | 1997-04-15 | ヤーマン株式会社 | Optical hair removal device |
US5782249A (en) | 1996-09-30 | 1998-07-21 | Weber; Paul J. | Laser manicure process |
US6424852B1 (en) | 1996-10-18 | 2002-07-23 | Lucid, Inc. | System for confocal imaging within dermal tissue |
JP3365227B2 (en) | 1996-10-25 | 2003-01-08 | 花王株式会社 | Method and apparatus for measuring optical properties of skin surface condition |
US7036516B1 (en) | 1996-10-30 | 2006-05-02 | Xantech Pharmaceuticals, Inc. | Treatment of pigmented tissues using optical energy |
US6228075B1 (en) | 1996-11-07 | 2001-05-08 | Cynosure, Inc. | Alexandrite laser system for hair removal |
GB9623627D0 (en) | 1996-11-13 | 1997-01-08 | Meditech International Inc | Method and apparatus for photon therapy |
CN1073607C (en) | 1996-11-20 | 2001-10-24 | 中国科学院近代物理研究所 | Electronic radiation solidifying paint for building material surface |
US6517532B1 (en) | 1997-05-15 | 2003-02-11 | Palomar Medical Technologies, Inc. | Light energy delivery head |
US6653618B2 (en) | 2000-04-28 | 2003-11-25 | Palomar Medical Technologies, Inc. | Contact detecting method and apparatus for an optical radiation handpiece |
US6273884B1 (en) | 1997-05-15 | 2001-08-14 | Palomar Medical Technologies, Inc. | Method and apparatus for dermatology treatment |
US6015404A (en) | 1996-12-02 | 2000-01-18 | Palomar Medical Technologies, Inc. | Laser dermatology with feedback control |
US20060149343A1 (en) | 1996-12-02 | 2006-07-06 | Palomar Medical Technologies, Inc. | Cooling system for a photocosmetic device |
US7204832B2 (en) | 1996-12-02 | 2007-04-17 | Pálomar Medical Technologies, Inc. | Cooling system for a photo cosmetic device |
US6162211A (en) | 1996-12-05 | 2000-12-19 | Thermolase Corporation | Skin enhancement using laser light |
FR2756741B1 (en) | 1996-12-05 | 1999-01-08 | Cird Galderma | USE OF A CHROMOPHORE IN A COMPOSITION INTENDED TO BE APPLIED TO THE SKIN BEFORE LASER TREATMENT |
DE19654108C2 (en) | 1996-12-23 | 2001-10-04 | Massholder Karl F | Cleaning system and method for cleaning a surface |
US5879159A (en) | 1996-12-24 | 1999-03-09 | Ion Laser Technology, Inc. | Portable high power arc lamp system and applications therefor |
US6063108A (en) | 1997-01-06 | 2000-05-16 | Salansky; Norman | Method and apparatus for localized low energy photon therapy (LEPT) |
US6391283B1 (en) | 1997-01-10 | 2002-05-21 | Ultradent Products, Inc. | Methods and apparatus for activating dental compositions |
US5830208A (en) | 1997-01-31 | 1998-11-03 | Laserlite, Llc | Peltier cooled apparatus and methods for dermatological treatment |
US5906609A (en) | 1997-02-05 | 1999-05-25 | Sahar Technologies | Method for delivering energy within continuous outline |
US5810801A (en) | 1997-02-05 | 1998-09-22 | Candela Corporation | Method and apparatus for treating wrinkles in skin using radiation |
US6200309B1 (en) | 1997-02-13 | 2001-03-13 | Mcdonnell Douglas Corporation | Photodynamic therapy system and method using a phased array raman laser amplifier |
US5836877A (en) | 1997-02-24 | 1998-11-17 | Lucid Inc | System for facilitating pathological examination of a lesion in tissue |
US6171302B1 (en) | 1997-03-19 | 2001-01-09 | Gerard Talpalriu | Apparatus and method including a handpiece for synchronizing the pulsing of a light source |
AU6569198A (en) | 1997-03-19 | 1998-10-12 | Lucid Technologies, Inc. | Cellular surgery utilizing confocal microscopy |
US5891063A (en) | 1997-04-03 | 1999-04-06 | Vigil; Arlene | Skin rejuvinating system |
DE29705934U1 (en) | 1997-04-03 | 1997-06-05 | Kaltenbach & Voigt | Diagnostic and treatment device for teeth |
US6317624B1 (en) | 1997-05-05 | 2001-11-13 | The General Hospital Corporation | Apparatus and method for demarcating tumors |
US6235015B1 (en) | 1997-05-14 | 2001-05-22 | Applied Optronics Corporation | Method and apparatus for selective hair depilation using a scanned beam of light at 600 to 1000 nm |
US6117129A (en) | 1997-05-30 | 2000-09-12 | Nidek Co., Ltd. | Laser treatment apparatus |
US6030399A (en) | 1997-06-04 | 2000-02-29 | Spectrx, Inc. | Fluid jet blood sampling device and methods |
US20020018754A1 (en) | 1999-03-15 | 2002-02-14 | Paul Albert Sagel | Shapes for tooth whitening strips |
DE19724299C2 (en) | 1997-06-09 | 2003-03-27 | Sli Lichtsysteme Gmbh | Method and device for the cosmetic treatment of acne vulgaris |
EP0885629A3 (en) | 1997-06-16 | 1999-07-21 | Danish Dermatologic Development A/S | Light pulse generating apparatus and cosmetic and therapeutic phototreatment |
US6475211B2 (en) | 1997-06-17 | 2002-11-05 | Cool Laser Optics, Inc. | Method and apparatus for temperature control of biologic tissue with simultaneous irradiation |
US5883471A (en) | 1997-06-20 | 1999-03-16 | Polycom, Inc. | Flashlamp pulse shaper and method |
AU8155098A (en) | 1997-06-20 | 1999-01-04 | Biolase Technology, Inc. | Electromagnetic radiation emitting toothbrush and dentifrice system |
US5968034A (en) | 1997-06-24 | 1999-10-19 | Laser Aesthetics, Inc. | Pulsed filament lamp for dermatological treatment |
US5885274A (en) | 1997-06-24 | 1999-03-23 | New Star Lasers, Inc. | Filament lamp for dermatological treatment |
US6142650A (en) | 1997-07-10 | 2000-11-07 | Brown; David C. | Laser flashlight |
US6058937A (en) | 1997-07-18 | 2000-05-09 | Miravant Systems, Inc. | Photodynamic Therapy of highly vascularized tissue |
US5921926A (en) | 1997-07-28 | 1999-07-13 | University Of Central Florida | Three dimensional optical imaging colposcopy |
US6104959A (en) * | 1997-07-31 | 2000-08-15 | Microwave Medical Corp. | Method and apparatus for treating subcutaneous histological features |
JP4014255B2 (en) | 1997-07-31 | 2007-11-28 | 有限会社開発顧問室 | Laser irradiation device for skin treatment |
US6273885B1 (en) * | 1997-08-16 | 2001-08-14 | Cooltouch Corporation | Handheld photoepilation device and method |
US6251127B1 (en) | 1997-08-25 | 2001-06-26 | Advanced Photodynamic Technologies, Inc. | Dye treatment solution and photodynamic therapy and method of using same |
CA2302044C (en) | 1997-08-25 | 2011-07-05 | Advanced Photodynamic Technologies, Inc. | Treatment device for topical photodynamic therapy and method of making same |
US6074382A (en) * | 1997-08-29 | 2000-06-13 | Asah Medico A/S | Apparatus for tissue treatment |
US6171300B1 (en) | 1997-09-04 | 2001-01-09 | Linvatec Corporation | Tubing cassette and method for cooling a surgical handpiece |
JP3019207B2 (en) | 1997-09-11 | 2000-03-13 | 川崎重工業株式会社 | Excavation equipment for shield machine |
US5813855A (en) | 1997-09-23 | 1998-09-29 | Crisio, Jr.; Raymond A. | Illuminated toothbrush |
US6176854B1 (en) | 1997-10-08 | 2001-01-23 | Robert Roy Cone | Percutaneous laser treatment |
US5984915A (en) | 1997-10-08 | 1999-11-16 | Trimedyne, Inc. | Percutaneous laser treatment |
DE19841217B4 (en) | 1997-10-27 | 2005-06-16 | Applied Photonics Worldwide, Inc., Reno | Apparatus and method for the spectroscopic analysis of human or animal tissue or body fluids |
US20010048077A1 (en) | 1997-10-27 | 2001-12-06 | Afanassieva Natalia I. | Apparatus and method for spectroscopic analysis of human or animal tissue or body fluids |
US5968033A (en) | 1997-11-03 | 1999-10-19 | Fuller Research Corporation | Optical delivery system and method for subsurface tissue irradiation |
US6229831B1 (en) | 1997-12-08 | 2001-05-08 | Coherent, Inc. | Bright diode-laser light-source |
US5949222A (en) | 1997-12-08 | 1999-09-07 | Buono; Robert N. | Self-oscillating switch mode DC to DC conversion with current switching threshold hystersis |
FR2772274B1 (en) | 1997-12-16 | 2002-01-04 | Galderma Rech Dermatologique | DEVICE COMPRISING A CHROMOPHORE COMPOSITION FOR APPLICATION ON THE SKIN, METHOD FOR MANUFACTURING SUCH A DEVICE AND USES THEREOF |
US6007219A (en) | 1997-12-17 | 1999-12-28 | O'meara; James C. | Laser lighting system |
US6325769B1 (en) | 1998-12-29 | 2001-12-04 | Collapeutics, Llc | Method and apparatus for therapeutic treatment of skin |
US6113559A (en) | 1997-12-29 | 2000-09-05 | Klopotek; Peter J. | Method and apparatus for therapeutic treatment of skin with ultrasound |
IL122840A (en) | 1997-12-31 | 2002-04-21 | Radiancy Inc | Apparatus and methods for removing hair |
WO1999034868A1 (en) | 1998-01-07 | 1999-07-15 | Kim Robin Segal | Diode laser irradiation and electrotherapy system for biological tissue stimulation |
US6200134B1 (en) | 1998-01-20 | 2001-03-13 | Kerr Corporation | Apparatus and method for curing materials with radiation |
RU2175873C2 (en) | 1998-01-23 | 2001-11-20 | Альтшулер Григорий Борисович | Method and device for carrying out light-induced treatment of materials, mainly biological tissues |
US7048731B2 (en) | 1998-01-23 | 2006-05-23 | Laser Abrasive Technologies, Llc | Methods and apparatus for light induced processing of biological tissues and of dental materials |
CN1058905C (en) | 1998-01-25 | 2000-11-29 | 重庆海扶(Hifu)技术有限公司 | High-intensity focus supersonic tumor scanning therapy system |
DE19803460C1 (en) | 1998-01-30 | 1999-08-12 | Dornier Medizintechnik | Application device for the treatment of biological tissue with laser radiation |
US6162055A (en) | 1998-02-13 | 2000-12-19 | Britesmile, Inc. | Light activated tooth whitening composition and method of using same |
US6416319B1 (en) | 1998-02-13 | 2002-07-09 | Britesmile, Inc. | Tooth whitening device and method of using same |
US6149644A (en) | 1998-02-17 | 2000-11-21 | Altralight, Inc. | Method and apparatus for epidermal treatment with computer controlled moving focused infrared light |
US6149895A (en) | 1998-02-17 | 2000-11-21 | Kreativ, Inc | Dental bleaching compositions, kits & methods |
US6080146A (en) | 1998-02-24 | 2000-06-27 | Altshuler; Gregory | Method and apparatus for hair removal |
IL123437A0 (en) | 1998-02-24 | 1998-09-24 | Shalev Pinchas | Apparatus and method for photothermal destruction of oral bacteria |
US6029303A (en) | 1998-03-04 | 2000-02-29 | Dewan; Raman N. | Electronic toothbrush |
US6173202B1 (en) | 1998-03-06 | 2001-01-09 | Spectrx, Inc. | Method and apparatus for enhancing flux rates of a fluid in a microporated biological tissue |
US6530915B1 (en) | 1998-03-06 | 2003-03-11 | Spectrx, Inc. | Photothermal structure for biomedical applications, and method therefor |
WO1999044638A1 (en) | 1998-03-06 | 1999-09-10 | Spectrx, Inc. | Photothermal structure for biomedical applications, and method therefor |
US6022316A (en) | 1998-03-06 | 2000-02-08 | Spectrx, Inc. | Apparatus and method for electroporation of microporated tissue for enhancing flux rates for monitoring and delivery applications |
EP1566149A1 (en) | 1998-03-12 | 2005-08-24 | Palomar Medical Technologies, Inc. | System for electromagnetic radiation of the skin |
US5920374A (en) | 1998-03-24 | 1999-07-06 | Board Of Trustees Of The University Of Arkansas | Computerized screening device utilizing the Pulfrich effect |
ES2403359T3 (en) | 1998-03-27 | 2013-05-17 | The General Hospital Corporation | Procedure and apparatus for the selective determination of lipid rich tissues |
EP0947173A1 (en) | 1998-03-30 | 1999-10-06 | Gabriel Bernaz | Probe for high frequency treatment of the skin |
US6306130B1 (en) | 1998-04-07 | 2001-10-23 | The General Hospital Corporation | Apparatus and methods for removing blood vessels |
US6264649B1 (en) | 1998-04-09 | 2001-07-24 | Ian Andrew Whitcroft | Laser treatment cooling head |
RU2145247C1 (en) | 1998-04-10 | 2000-02-10 | Жаров Владимир Павлович | Photomatrix therapeutic device for treatment of extended pathologies |
US6223071B1 (en) | 1998-05-01 | 2001-04-24 | Dusa Pharmaceuticals Inc. | Illuminator for photodynamic therapy and diagnosis which produces substantially uniform intensity visible light |
US5974616A (en) | 1998-05-26 | 1999-11-02 | Dreyfus; Edward | Sound producing toothbrush |
US6099521A (en) | 1998-05-26 | 2000-08-08 | Shadduck; John H. | Semiconductor contact lens cooling system and technique for light-mediated eye therapies |
US6030378A (en) | 1998-05-26 | 2000-02-29 | Stewart; Bob W. | Method of hair removal by transcutaneous application of laser light |
US6110195A (en) | 1998-06-01 | 2000-08-29 | Altralight, Inc. | Method and apparatus for surgical and dermatological treatment by multi-wavelength laser light |
US6029304A (en) | 1998-06-09 | 2000-02-29 | Colgate-Palmolive Company | Light interactive toothbrush |
US6080147A (en) | 1998-06-10 | 2000-06-27 | Tobinick; Edward L. | Method of employing a flashlamp for removal of hair, veins and capillaries |
DE19827417B4 (en) | 1998-06-19 | 2004-10-28 | Hahn, Rainer, Dr.Med.Dent. | Material for different modification of the optical properties of different cells |
US6319274B1 (en) | 1998-06-22 | 2001-11-20 | John H. Shadduck | Devices and techniques for light-mediated stimulation of trabecular meshwork in glaucoma therapy |
US6416531B2 (en) | 1998-06-24 | 2002-07-09 | Light Sciences Corporation | Application of light at plural treatment sites within a tumor to increase the efficacy of light therapy |
ATE428345T1 (en) | 1998-07-09 | 2009-05-15 | Curelight Medical Ltd | DEVICE AND METHOD FOR EFFECTIVE HIGH-ENERGY PHOTODYNAMIC THERAPY OF ACNE VULGARIS AND SEBORRHEA |
WO2000003257A1 (en) | 1998-07-13 | 2000-01-20 | Sigma Systems Corporation | Thermal platform and method |
US5941701A (en) | 1998-07-14 | 1999-08-24 | Ceramoptec Ind Inc | Device and method to treat oral disease in felines |
JP2000037400A (en) | 1998-07-23 | 2000-02-08 | Nippon Sekigaisen Kogyo Kk | Front surface cooling method at the time of laser irradiation |
US6236891B1 (en) | 1998-07-31 | 2001-05-22 | Surx, Inc. | Limited heat transfer devices and methods to shrink tissues |
GB9816914D0 (en) | 1998-08-05 | 1998-09-30 | Smithkline Beecham Gmbh | Novel device |
US6126655A (en) | 1998-08-11 | 2000-10-03 | The General Hospital Corporation | Apparatus and method for selective laser-induced heating of biological tissue |
DE19836649C2 (en) | 1998-08-13 | 2002-12-19 | Zeiss Carl Meditec Ag | Medical handpiece |
US6440155B1 (en) | 1998-08-19 | 2002-08-27 | Tokai University Educational System | Device for heating a biotissue employing a strong light |
US6525819B1 (en) | 1998-09-02 | 2003-02-25 | Pocketspec Technologies Inc. | Colorimeter for dental applications |
JP3390755B2 (en) | 1998-09-29 | 2003-03-31 | 科学技術振興事業団 | Wavelength tunable short pulse light generating apparatus and method |
US6595986B2 (en) | 1998-10-15 | 2003-07-22 | Stephen Almeida | Multiple pulse photo-dermatological device |
US6059820A (en) | 1998-10-16 | 2000-05-09 | Paradigm Medical Corporation | Tissue cooling rod for laser surgery |
KR100280821B1 (en) | 1998-11-18 | 2001-03-02 | 정선종 | Tunable Fiber Laser |
JP2000153003A (en) | 1998-11-24 | 2000-06-06 | Ya Man Ltd | Cooling probe for laser beauty culture instrument |
CZ287832B6 (en) | 1998-11-24 | 2001-02-14 | I.B.C., A. S. | Device for light therapy |
US6096209A (en) | 1998-11-25 | 2000-08-01 | Aws Industries, L.L.C. | Three media silver recovery apparatus |
WO2000036715A1 (en) | 1998-11-25 | 2000-06-22 | The University Of New Mexico | Precisely wavelength-tunable and wavelength-switchable narrow linewidth lasers |
US6887260B1 (en) | 1998-11-30 | 2005-05-03 | Light Bioscience, Llc | Method and apparatus for acne treatment |
US6663659B2 (en) | 2000-01-13 | 2003-12-16 | Mcdaniel David H. | Method and apparatus for the photomodulation of living cells |
US6936044B2 (en) | 1998-11-30 | 2005-08-30 | Light Bioscience, Llc | Method and apparatus for the stimulation of hair growth |
US6283956B1 (en) | 1998-11-30 | 2001-09-04 | David H. McDaniels | Reduction, elimination, or stimulation of hair growth |
US6514242B1 (en) | 1998-12-03 | 2003-02-04 | David Vasily | Method and apparatus for laser removal of hair |
US6183500B1 (en) | 1998-12-03 | 2001-02-06 | Sli Lichtsysteme Gmbh | Process and apparatus for the cosmetic treatment of acne vulgaris |
US6106293A (en) | 1998-12-04 | 2000-08-22 | Wiesel; Peter E. | Methods for whitening teeth |
US6402739B1 (en) | 1998-12-08 | 2002-06-11 | Y-Beam Technologies, Inc. | Energy application with cooling |
US6183773B1 (en) | 1999-01-04 | 2001-02-06 | The General Hospital Corporation | Targeting of sebaceous follicles as a treatment of sebaceous gland disorders |
US6370180B2 (en) | 1999-01-08 | 2002-04-09 | Corning Incorporated | Semiconductor-solid state laser optical waveguide pump |
US6220772B1 (en) | 1999-01-13 | 2001-04-24 | Optiva Corporation | Fluid-dispensing and refilling system for a power toothbrush |
US6402410B1 (en) | 1999-01-13 | 2002-06-11 | Philips Oral Healthcare | Fluid-dispensing and refilling system for a power toothbrush |
SE522249C2 (en) | 1999-01-13 | 2004-01-27 | Biolight Patent Holding Ab | Control device for controlling external processing by light |
SE515992C2 (en) | 1999-01-20 | 2001-11-05 | Biolight Patent Holding Ab | Light emitting organs for medical treatment are externalized by light |
AU2091100A (en) | 1999-01-25 | 2000-08-07 | Jilin Zhu | The optical quantum medical technology and the instrument thereof |
US6159236A (en) | 1999-01-28 | 2000-12-12 | Advanced Photodynamic Technologies, Inc. | Expandable treatment device for photodynamic therapy and method of using same |
US6202242B1 (en) | 1999-01-29 | 2001-03-20 | Zephyr Design, Inc. | Light emitting electric toothbrush |
WO2000044294A1 (en) | 1999-01-29 | 2000-08-03 | Welch Allyn, Inc. | Apparatus and method of photo-specific tissue treatment |
USD424197S (en) | 1999-02-12 | 2000-05-02 | Thermolase Corporation | Laser handpiece housing |
US6187029B1 (en) | 1999-03-02 | 2001-02-13 | Physician's Technology, Llc | Photo-thermal treatment device |
US6491685B2 (en) | 1999-03-04 | 2002-12-10 | The Regents Of The University Of California | Laser and acoustic lens for lithotripsy |
GB9905173D0 (en) | 1999-03-05 | 1999-04-28 | Sls Biophile Limited | Wrinkle reduction |
AU3147200A (en) | 1999-03-08 | 2000-09-28 | Asah Medico A/S | An apparatus for tissue treatment and having a monitor for display of tissue features |
JP3188426B2 (en) | 1999-03-12 | 2001-07-16 | ヤーマン株式会社 | Laser irradiation probe |
US6106294A (en) | 1999-03-15 | 2000-08-22 | Daniel; Martin K. | Lighting toothbrush and method of use |
US6569155B1 (en) | 1999-03-15 | 2003-05-27 | Altus Medical, Inc. | Radiation delivery module and dermal tissue treatment method |
US6383176B1 (en) | 1999-03-15 | 2002-05-07 | Altus Medical, Inc. | Hair removal device and method |
US6235016B1 (en) | 1999-03-16 | 2001-05-22 | Bob W. Stewart | Method of reducing sebum production by application of pulsed light |
RU2181571C2 (en) | 1999-03-18 | 2002-04-27 | Закрытое акционерное общество "LC" | Device and method for performing therapeutic and cosmetic phototreatment of biological tissue |
US6312451B1 (en) | 1999-03-23 | 2001-11-06 | Jackson Streeter | Low level laser therapy apparatus |
DE19914108A1 (en) | 1999-03-23 | 2000-10-05 | Plasmaphotonics Gmbh | Irradiation arrangement, in particular for optical thermolysis |
US6267779B1 (en) | 1999-03-29 | 2001-07-31 | Medelaser, Llc | Method and apparatus for therapeutic laser treatment |
US6484052B1 (en) | 1999-03-30 | 2002-11-19 | The Regents Of The University Of California | Optically generated ultrasound for enhanced drug delivery |
WO2000062700A1 (en) | 1999-04-14 | 2000-10-26 | Koninklijke Philips Electronics N.V. | Hair-removing device with a controllable laser source |
US6709269B1 (en) | 2000-04-14 | 2004-03-23 | Gregory B. Altshuler | Apparatus and method for the processing of solid materials, including hard tissues |
US6162212A (en) | 1999-04-19 | 2000-12-19 | Esc Medical Systems, Ltd. | Optimal procedure for performing a hair removal |
JP2000300684A (en) | 1999-04-20 | 2000-10-31 | Nidek Co Ltd | Laser therapeutic equipment |
WO2000064537A1 (en) | 1999-04-27 | 2000-11-02 | The General Hospital Corporation Doing Business As Massachusetts General Hospital | Phototherapy method for treatment of acne |
US6439888B1 (en) | 1999-05-03 | 2002-08-27 | Pls Liquidating Llc | Optical source and method |
RU2182025C2 (en) | 1999-05-05 | 2002-05-10 | Миржалил Хамитович Усманов | Fire-proofing device |
US6606755B1 (en) | 1999-05-24 | 2003-08-19 | American Applied Technology | Electronically timed toothbrush system |
WO2000071045A1 (en) | 1999-05-25 | 2000-11-30 | International Technologies (Lasers), Ltd. | Laser for skin treatment |
EP1057454A3 (en) | 1999-05-31 | 2003-11-12 | Nidek Co., Ltd. | Laser skin treatment apparatus |
US6733492B2 (en) | 1999-05-31 | 2004-05-11 | Nidek Co., Ltd. | Laser treatment apparatus |
GB9912998D0 (en) | 1999-06-04 | 1999-08-04 | Sls Biophile Limited | Depilation |
US7371408B1 (en) | 1999-06-07 | 2008-05-13 | Wright Medical Technology, Inc. | Bone graft substitute composition |
US6685699B1 (en) | 1999-06-09 | 2004-02-03 | Spectrx, Inc. | Self-removing energy absorbing structure for thermal tissue ablation |
EP1182982A1 (en) | 1999-06-09 | 2002-03-06 | Spectrx, Inc. | Self-removing energy absorbing structure for thermal tissue ablation |
EP1187572A1 (en) | 1999-06-18 | 2002-03-20 | Spectrx, Inc. | Light beam generation and focusing device |
DE60002336T2 (en) | 1999-07-02 | 2004-03-04 | Asah Medico A/S | LASER CRYSTAL DEVICE |
US20030216795A1 (en) | 1999-07-07 | 2003-11-20 | Yoram Harth | Apparatus and method for high energy photodynamic therapy of acne vulgaris, seborrhea and other skin disorders |
US20020128695A1 (en) | 1999-07-07 | 2002-09-12 | Yoram Harth | Apparatus and method for high energy photodynamic therapy of acne vulgaris and seborrhea |
US20040122492A1 (en) | 1999-07-07 | 2004-06-24 | Yoram Harth | Phototherapeutic treatment of skin conditions |
US6210425B1 (en) | 1999-07-08 | 2001-04-03 | Light Sciences Corporation | Combined imaging and PDT delivery system |
JP3340090B2 (en) | 1999-07-19 | 2002-10-28 | ヤーマン株式会社 | Laser hair removal probe |
US6451007B1 (en) | 1999-07-29 | 2002-09-17 | Dale E. Koop | Thermal quenching of tissue |
US6413267B1 (en) | 1999-08-09 | 2002-07-02 | Theralase, Inc. | Therapeutic laser device and method including noninvasive subsurface monitoring and controlling means |
US6290713B1 (en) | 1999-08-24 | 2001-09-18 | Thomas A. Russell | Flexible illuminators for phototherapy |
DE19944401A1 (en) | 1999-09-16 | 2001-03-22 | Laser & Med Tech Gmbh | Depth/structure-selective biological tissue treatment method and device e.g. for body hair removal, uses simultaneous application of pressure and irradiation with light |
DE19945416C1 (en) | 1999-09-22 | 2001-04-26 | Siemens Ag | Cooling arrangement for X-ray emitter for computer tomograph enables the X-ray source to be operated over longer periods |
US6331111B1 (en) | 1999-09-24 | 2001-12-18 | Cao Group, Inc. | Curing light system useful for curing light activated composite materials |
GB2356570A (en) | 1999-09-30 | 2001-05-30 | Oe Lys Ltd | Acne treating apparatus based on the emission of light in three different ranges of wavelength |
US6406474B1 (en) | 1999-09-30 | 2002-06-18 | Ceramoptec Ind Inc | Device and method for application of radiation |
US6758845B1 (en) | 1999-10-08 | 2004-07-06 | Lumenis Inc. | Automatic firing apparatus and methods for laser skin treatment over large areas |
US6355054B1 (en) | 1999-11-05 | 2002-03-12 | Ceramoptec Industries, Inc. | Laser system for improved transbarrier therapeutic radiation delivery |
US6358242B1 (en) | 1999-11-12 | 2002-03-19 | Ceramoptec Industries, Inc. | Post laser treatment for permanent hair removal |
JP2001145520A (en) | 1999-11-19 | 2001-05-29 | Sharion Kk | Far infrared rays mask |
US6527764B1 (en) | 1999-12-02 | 2003-03-04 | Ceramoptec Industries, Inc. | Device and method for laser biomodulation in PDT/surgery |
US6743222B2 (en) | 1999-12-10 | 2004-06-01 | Candela Corporation | Method of treating disorders associated with sebaceous follicles |
DE19959508A1 (en) | 1999-12-10 | 2001-06-13 | Schaeffler Waelzlager Ohg | Guide rail for a linear bearing |
US6354370B1 (en) | 1999-12-16 | 2002-03-12 | The United States Of America As Represented By The Secretary Of The Air Force | Liquid spray phase-change cooling of laser devices |
US6595934B1 (en) | 2000-01-19 | 2003-07-22 | Medtronic Xomed, Inc. | Methods of skin rejuvenation using high intensity focused ultrasound to form an ablated tissue area containing a plurality of lesions |
IL150604A0 (en) | 2000-01-25 | 2003-02-12 | Palomar Medical Tech Inc | Method and apparatus for medical treatment utilizing long duration electromagnetic radiation |
US6669688B2 (en) | 2000-01-25 | 2003-12-30 | The Regents Of The University Of California | Method and apparatus for measuring the heat transfer coefficient during cryogen spray cooling of tissue |
AU2001239835A1 (en) | 2000-02-26 | 2001-09-03 | Advanced Photodynamic Technologies, Inc. | Photodynamic cellular and acellular organism eradication utilizing a photosensitive material and surfactant |
US6261595B1 (en) | 2000-02-29 | 2001-07-17 | Zars, Inc. | Transdermal drug patch with attached pocket for controlled heating device |
JP2001238968A (en) | 2000-03-01 | 2001-09-04 | Ya Man Ltd | Laser beam irradiation probe |
US7320593B2 (en) | 2000-03-08 | 2008-01-22 | Tir Systems Ltd. | Light emitting diode light source for curing dental composites |
US6436094B1 (en) | 2000-03-16 | 2002-08-20 | Laserscope, Inc. | Electromagnetic and laser treatment and cooling device |
GB2370992B (en) | 2000-03-23 | 2002-11-20 | Photo Therapeutics Ltd | Therapeutic light source and method |
US6749623B1 (en) | 2000-03-31 | 2004-06-15 | Richard A Hsi | Method and apparatus for catheter phototherapy with dose sensing |
GB2360946B (en) | 2000-04-08 | 2002-06-12 | Lynton Lasers Ltd | Dermatological treatment apparatus |
AU2001257069A1 (en) | 2000-04-17 | 2001-10-30 | Medelaser, Llc | Photostimulaton treatment apparatus and methods for use |
GB2361430A (en) | 2000-04-17 | 2001-10-24 | Photo Therapeutics Ltd | Therapeutic discharge lamps |
US6554439B1 (en) | 2000-05-15 | 2003-04-29 | The Mclean Hospital | Illumination apparatus for simulating dynamic light conditions |
US6551346B2 (en) | 2000-05-17 | 2003-04-22 | Kent Crossley | Method and apparatus to prevent infections |
US9820883B2 (en) | 2000-05-19 | 2017-11-21 | Michael S. Berlin | Method for treating glaucoma |
JP2002011106A (en) | 2000-06-28 | 2002-01-15 | Nidek Co Ltd | Laser therapeutic apparatus |
GB2364376A (en) | 2000-07-05 | 2002-01-23 | Astron Clinica Ltd | Skin illumination and examination apparatus |
DE10033256A1 (en) | 2000-07-10 | 2002-01-24 | Coronet Werke Gmbh | Method and device for producing bristle goods and bristle goods |
US6471716B1 (en) | 2000-07-11 | 2002-10-29 | Joseph P. Pecukonis | Low level light therapy method and apparatus with improved wavelength, temperature and voltage control |
JP3868724B2 (en) | 2000-07-18 | 2007-01-17 | 独立行政法人科学技術振興機構 | Ultrasound angioscope system |
EP1341464A4 (en) | 2000-07-21 | 2009-07-22 | Ceramoptec Gmbh | Treatment for epithelial diseases |
AU2000264703A1 (en) | 2000-07-31 | 2002-02-13 | El. En. S.P.A. | Method and device for epilation by ultrasound |
DE20014735U1 (en) | 2000-08-25 | 2000-10-12 | B & P Ag Roschacherberg | Light therapy device |
US6702808B1 (en) | 2000-09-28 | 2004-03-09 | Syneron Medical Ltd. | Device and method for treating skin |
US6471712B2 (en) | 2000-10-05 | 2002-10-29 | Steven A. Burres | Dermabrasion and skin care apparatus |
US6435873B1 (en) | 2000-10-10 | 2002-08-20 | 3M Innovative Properties Company | Medication delivery devices |
GB2368020A (en) | 2000-10-18 | 2002-04-24 | Icn Photonics Ltd | Treatment of acne vulgaris skin condition by irradiation with light of specific wavelengths to target specific chromophores & stimulate collagen production |
DE10052296C1 (en) | 2000-10-20 | 2002-04-04 | Braun Gmbh | Electrically-operated hair removal device has pulsed stroboscopic light signal provided by illumination device for illumination of relatively moving working elements |
US6506053B2 (en) | 2000-11-13 | 2003-01-14 | Peter E. Wiesel | Systems for treating teeth |
US6616447B1 (en) | 2000-11-15 | 2003-09-09 | Biolase Technology, Inc. | Device for dental care and whitening |
US20020071287A1 (en) | 2000-12-13 | 2002-06-13 | 3M Innovative Properties Company | Laser pointer with multiple color beams |
US6808532B2 (en) | 2000-12-15 | 2004-10-26 | Dan E. Andersen | Laser treatment for reducing wrinkles |
US6746444B2 (en) | 2000-12-18 | 2004-06-08 | Douglas J. Key | Method of amplifying a beneficial selective skin response to light energy |
JP2005502385A (en) | 2000-12-28 | 2005-01-27 | パロマー・メディカル・テクノロジーズ・インコーポレーテッド | Method and apparatus for performing skin therapy EMR treatment |
US20080183162A1 (en) | 2000-12-28 | 2008-07-31 | Palomar Medical Technologies, Inc. | Methods And Devices For Fractional Ablation Of Tissue |
US6623513B2 (en) | 2001-01-19 | 2003-09-23 | Advanced Photodynamic Technologies, Inc. | Apparatus and method of photodynamic eradication of organisms utilizing pyrrolnitrin |
CA2444891A1 (en) | 2001-01-22 | 2002-08-15 | Eric Larsen | Photodynamic stimulation device and methods |
ITMO20010008A1 (en) | 2001-01-29 | 2002-07-29 | Laserwave Srl | DEVICE FOR SKIN TREATMENTS |
DE60226964D1 (en) | 2001-02-12 | 2008-07-17 | Koninkl Philips Electronics Nv | SCHALLANTRIEBS TOOTHBRUSH WITH MULTIPLE CONTAINERS |
US6673095B2 (en) | 2001-02-12 | 2004-01-06 | Wound Healing Of Oklahoma, Inc. | Apparatus and method for delivery of laser light |
US8106038B2 (en) | 2001-02-15 | 2012-01-31 | Qlt Inc. | Method for reducing or preventing PDT related inflammation |
US20030023284A1 (en) | 2001-02-20 | 2003-01-30 | Vladimir Gartstein | Method and apparatus for the in-vivo treatment of pathogens |
JP4034941B2 (en) | 2001-02-28 | 2008-01-16 | 株式会社ニデック | Laser therapy device |
US20020149326A1 (en) | 2001-03-01 | 2002-10-17 | Mikhail Inochkin | Flashlamp drive circuit |
US6888319B2 (en) | 2001-03-01 | 2005-05-03 | Palomar Medical Technologies, Inc. | Flashlamp drive circuit |
EP1665996A3 (en) | 2001-03-02 | 2007-11-28 | Palomar Medical Technologies, Inc. | Apparatus and method for photocosmetic and photodermatological treatment |
DE10112289A1 (en) | 2001-03-08 | 2002-09-26 | Optomed Optomedical Systems Gmbh | Irradiating device used for treating acne comprises a radiation source emitting a broad band spectrum in a specified region and operating in the pulse manner |
DE10123926A1 (en) | 2001-03-08 | 2002-09-19 | Optomed Optomedical Systems Gmbh | irradiation device |
US6503486B2 (en) | 2001-03-12 | 2003-01-07 | Colgate Palmolive Company | Strip for whitening tooth surfaces |
GB0107853D0 (en) | 2001-03-29 | 2001-05-23 | Asclepion Meditec Ltd | Hand apparatus for light delivery |
WO2002078559A1 (en) | 2001-03-30 | 2002-10-10 | Koninklijke Philips Electronics N.V. | Skin treating device comprising a protected radiation exit opening |
US7107996B2 (en) | 2001-04-10 | 2006-09-19 | Ganz Robert A | Apparatus and method for treating atherosclerotic vascular disease through light sterilization |
DE50107938D1 (en) | 2001-04-18 | 2005-12-08 | Georg Knott | IRRADIATOR IN PARTICULAR TO PHOTODYNAMIC DIAGNOSIS OR THERAPY |
DE10120787A1 (en) | 2001-04-25 | 2003-01-09 | Foerderung Von Medizin Bio Und | Remission-controlled device with laser handpiece for sensor-controlled selective laser therapy of blood vessels and skin tissues has multiple-sensor system e.g. using near infrared or visible radiation |
AU2002305313A1 (en) | 2001-04-30 | 2002-11-11 | Medtronic, Inc. | Implantable medical device and patch system |
US8840918B2 (en) | 2001-05-01 | 2014-09-23 | A. V. Topchiev Institute of Petrochemical Synthesis, Russian Academy of Sciences | Hydrogel compositions for tooth whitening |
EP1386145B8 (en) | 2001-05-04 | 2012-08-29 | Thermo Scientific Portable Analytical Instruments Inc. | X-ray fluorescence combined with laser induced photon spectroscopy |
US6572634B2 (en) | 2001-05-07 | 2003-06-03 | Myung H. Koo | Nose end adjusting device |
CN1879573B (en) | 2001-05-23 | 2012-05-30 | 帕洛玛医疗技术公司 | Cooling system for a photo cosmetic device |
DE10125772C2 (en) | 2001-05-26 | 2003-06-18 | Duerr Dental Gmbh Co Kg | Dental or endoscopic camera |
US6679837B2 (en) | 2001-06-01 | 2004-01-20 | Intlas Ltd. | Laser light irradiation apparatus |
WO2002102419A2 (en) | 2001-06-15 | 2002-12-27 | Uv-Solutions, Llc. | Method and apparatus for sterilizing or disinfecting a region through a bandage |
US6770069B1 (en) | 2001-06-22 | 2004-08-03 | Sciton, Inc. | Laser applicator |
EP1414516A2 (en) | 2001-06-26 | 2004-05-06 | Photomed Technologies, Inc. | Therapeutic methods using electromagnetic radiation |
AU2002316500A1 (en) | 2001-07-02 | 2003-01-21 | Palomar Medical Technologies, Inc. | Laser device for medical/cosmetic procedures |
US20030009158A1 (en) | 2001-07-09 | 2003-01-09 | Perricone Nicholas V. | Skin treatments using blue and violet light |
ITPD20010187A1 (en) | 2001-07-23 | 2003-01-23 | Cutech Srl | POLYPHERIC FOLLICLE TREATMENT, IN PARTICULAR AGAINST HAIR LOSS |
JP4485788B2 (en) | 2001-07-27 | 2010-06-23 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Apparatus for skin treatment having a processor for determining the dose of a radiation pulse |
US20030032900A1 (en) | 2001-08-08 | 2003-02-13 | Engii (2001) Ltd. | System and method for facial treatment |
JP2005500108A (en) | 2001-08-15 | 2005-01-06 | リライアント テクノロジーズ,インコーポレイティド | Apparatus and method for thermal excision of biological tissue |
US7094252B2 (en) | 2001-08-21 | 2006-08-22 | Cooltouch Incorporated | Enhanced noninvasive collagen remodeling |
US6942658B1 (en) | 2001-08-24 | 2005-09-13 | Boilase Technology, Inc. | Radiation emitting apparatus with spatially controllable output energy distributions |
AU2002341359A1 (en) | 2001-09-27 | 2003-04-07 | Galil Medical Ltd. | Apparatus and method for cryosurgical treatment of tumors of the breast |
US6561808B2 (en) | 2001-09-27 | 2003-05-13 | Ceramoptec Industries, Inc. | Method and tools for oral hygiene |
US7144248B2 (en) | 2001-10-18 | 2006-12-05 | Irwin Dean S | Device for oral UV photo-therapy |
US6629989B2 (en) | 2001-10-18 | 2003-10-07 | Shimadzu Corporation | Phototherapy device for pressure pain point therapy and trigger point therapy |
US6952856B2 (en) | 2001-11-06 | 2005-10-11 | Create Co., Ltd. | Ionic toothbrush |
US6648904B2 (en) | 2001-11-29 | 2003-11-18 | Palomar Medical Technologies, Inc. | Method and apparatus for controlling the temperature of a surface |
US20040147984A1 (en) | 2001-11-29 | 2004-07-29 | Palomar Medical Technologies, Inc. | Methods and apparatus for delivering low power optical treatments |
US6623272B2 (en) | 2001-11-30 | 2003-09-23 | Kathleen Clemans | Light-emitting toothbrush and method of whitening teeth |
WO2003049633A1 (en) | 2001-12-10 | 2003-06-19 | Inolase 2002 Ltd. | Method and apparatus for improving safety during exposure to a monochromatic light source |
EP1627662B1 (en) | 2004-06-10 | 2011-03-02 | Candela Corporation | Apparatus for vacuum-assisted light-based treatments of the skin |
US20040082940A1 (en) | 2002-10-22 | 2004-04-29 | Michael Black | Dermatological apparatus and method |
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 |
US20030216719A1 (en) | 2001-12-12 | 2003-11-20 | Len Debenedictis | Method and apparatus for treating skin using patterns of optical energy |
US6692252B2 (en) | 2001-12-17 | 2004-02-17 | Ultradent Products, Inc. | Heat sink with geometric arrangement of LED surfaces |
AU2002367397A1 (en) | 2001-12-27 | 2003-07-24 | Palomar Medical Technologies, Inc. | Method and apparatus for improved vascular related treatment |
JP2003192809A (en) | 2001-12-28 | 2003-07-09 | Mitsubishi Paper Mills Ltd | Heat resistant insulation sheet |
US6863781B2 (en) | 2002-02-26 | 2005-03-08 | Massachusetts Institute Of Technology | Process for photocatalysis and two-electron mixed-valence complexes |
EP1340486A1 (en) | 2002-03-01 | 2003-09-03 | Cognis France S.A. | Use of sugar esters |
US7081128B2 (en) | 2002-03-04 | 2006-07-25 | Hart Barry M | Phototherapy device and method of use |
US6927857B2 (en) | 2002-03-09 | 2005-08-09 | Kimberly-Clark Worldwide, Inc. | Process for the detection of marked components of a composite article using infrared blockers |
IL163946A0 (en) | 2002-03-12 | 2005-12-18 | Gen Hospital Corp | Method and apparatus for hair growth managment |
US8840608B2 (en) | 2002-03-15 | 2014-09-23 | The General Hospital Corporation | Methods and devices for selective disruption of fatty tissue by controlled cooling |
GB0301737D0 (en) | 2003-01-24 | 2003-02-26 | Enfis Ltd | Method and device for treatment of skin conditions |
US6955684B2 (en) | 2002-03-29 | 2005-10-18 | Savage Jr Henry C | Portable light delivery apparatus and methods |
US7647092B2 (en) | 2002-04-05 | 2010-01-12 | Massachusetts Institute Of Technology | Systems and methods for spectroscopy of biological tissue |
DE60324125D1 (en) | 2002-04-09 | 2008-11-27 | Altshuler Gregory | DEVICE FOR PROCESSING HARD MATERIALS |
US7322972B2 (en) | 2002-04-10 | 2008-01-29 | The Regents Of The University Of California | In vivo port wine stain, burn and melanin depth determination using a photoacoustic probe |
AU2003223613A1 (en) | 2002-04-16 | 2003-11-03 | Lumerx, Inc | Chemiluminescent light source using visible light for biotherapy |
GB2390021A (en) | 2002-05-17 | 2003-12-31 | Ian Charlesworth | Hand-held led apparatus for treating acne |
US7135033B2 (en) | 2002-05-23 | 2006-11-14 | Palomar Medical Technologies, Inc. | Phototreatment device for use with coolants and topical substances |
US20070038206A1 (en) | 2004-12-09 | 2007-02-15 | Palomar Medical Technologies, Inc. | Photocosmetic device |
JP2006500972A (en) | 2002-06-19 | 2006-01-12 | 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 | Method and apparatus for treating tissue at a depth by radiant heat |
BR0312430A (en) | 2002-06-19 | 2005-04-26 | Palomar Medical Tech Inc | Method and apparatus for treating skin and subcutaneous conditions |
US7201766B2 (en) | 2002-07-03 | 2007-04-10 | Life Support Technologies, Inc. | Methods and apparatus for light therapy |
US7001413B2 (en) | 2002-07-03 | 2006-02-21 | Life Support Technologies, Inc. | Methods and apparatus for light therapy |
FR2842088B1 (en) | 2002-07-10 | 2004-12-10 | Seb Sa | ELECTRIC KETTLE |
US20040015158A1 (en) | 2002-07-19 | 2004-01-22 | To-Mu Chen | Transilluminator device |
AU2003265308A1 (en) | 2002-07-25 | 2004-02-16 | Jonathan S. Dahm | Method and apparatus for using light emitting diodes for curing |
US6902397B2 (en) | 2002-08-01 | 2005-06-07 | Sunstar Americas, Inc. | Enhanced dental hygiene system with direct UVA photoexcitation |
US20070219605A1 (en) | 2006-03-20 | 2007-09-20 | Palomar Medical Technologies, Inc. | Treatment of tissue volume with radiant energy |
US20070213792A1 (en) | 2002-10-07 | 2007-09-13 | Palomar Medical Technologies, Inc. | Treatment Of Tissue Volume With Radiant Energy |
WO2004033040A1 (en) | 2002-10-07 | 2004-04-22 | Palomar Medical Technologies, Inc. | Apparatus for performing photobiostimulation |
WO2004043543A1 (en) | 2002-11-12 | 2004-05-27 | Palomar Medical Technologies, Inc. | Apparatus for performing optical dermatology |
US6866678B2 (en) | 2002-12-10 | 2005-03-15 | Interbational Technology Center | Phototherapeutic treatment methods and apparatus |
US6991644B2 (en) | 2002-12-12 | 2006-01-31 | Cutera, Inc. | Method and system for controlled spatially-selective epidermal pigmentation phototherapy with UVA LEDs |
AU2003301111A1 (en) | 2002-12-20 | 2004-07-22 | Palomar Medical Technologies, Inc. | Apparatus for light treatment of acne and other disorders of follicles |
US20040143920A1 (en) | 2003-01-24 | 2004-07-29 | Dr. Fresh, Inc. | Illuminated flashing toothbrush and method of use |
CN1771073A (en) | 2003-02-10 | 2006-05-10 | 帕洛玛医疗技术公司 | Light emitting oral appliance and method of use |
US20040161213A1 (en) | 2003-02-15 | 2004-08-19 | Tsung-Ting Lee | Fiber optic display device |
JP2006518266A (en) | 2003-02-19 | 2006-08-10 | 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 | Method and apparatus for treating fake folliculitis |
US20040176754A1 (en) | 2003-03-06 | 2004-09-09 | Island Tobin C. | Method and device for sensing skin contact |
US7006223B2 (en) | 2003-03-07 | 2006-02-28 | 3Gen, Llc. | Dermoscopy epiluminescence device employing cross and parallel polarization |
DE202004021226U1 (en) | 2003-03-27 | 2007-07-26 | The General Hospital Corp., Boston | Device for dermatological treatment and fractional surface renewal of the skin |
US7153298B1 (en) | 2003-03-28 | 2006-12-26 | Vandolay, Inc. | Vascular occlusion systems and methods |
US6989023B2 (en) | 2003-07-08 | 2006-01-24 | Oralum, Llc | Hygienic treatments of body structures |
US7144247B2 (en) | 2003-04-25 | 2006-12-05 | Oralum, Llc | Hygienic treatments of structures in body cavities |
US6953341B2 (en) | 2003-08-20 | 2005-10-11 | Oralum, Llc | Toothpick for light treatment of body structures |
US20040234460A1 (en) | 2003-05-21 | 2004-11-25 | Tarver Jeanna Gail | Tooth whitening compositions and methods for using the same |
JP2005027702A (en) | 2003-07-07 | 2005-02-03 | Ya Man Ltd | Face treatment mask |
WO2005007003A1 (en) | 2003-07-11 | 2005-01-27 | Reliant Technologies, Inc. | Method and apparatus for fractional photo therapy of skin |
US7291140B2 (en) | 2003-07-18 | 2007-11-06 | Cutera, Inc. | System and method for low average power dermatologic light treatment device |
US7145108B2 (en) | 2003-07-22 | 2006-12-05 | Kaz, Incorporated | Configurable heating pad controller |
US8623002B2 (en) | 2003-07-29 | 2014-01-07 | Koninklijke Philips N.V. | Electromagnetic radiation delivery apparatus |
US8083784B2 (en) | 2003-08-19 | 2011-12-27 | Photonx Health Corporation | Photon therapy method and apparatus |
US8870856B2 (en) | 2003-08-25 | 2014-10-28 | Cutera, Inc. | Method for heating skin using light to provide tissue treatment |
US7722600B2 (en) | 2003-08-25 | 2010-05-25 | Cutera, Inc. | System and method for heating skin using light to provide tissue treatment |
US20050049467A1 (en) | 2003-08-28 | 2005-03-03 | Georgios Stamatas | Method for assessing pigmented skin |
ITBO20030717A1 (en) | 2003-11-27 | 2005-05-28 | Espansione Marketing S P A | LIGHT IRRADIATION UNIT. |
US7220254B2 (en) | 2003-12-31 | 2007-05-22 | 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 |
US7041100B2 (en) | 2004-01-21 | 2006-05-09 | Syneron Medical Ltd. | Method and system for selective electro-thermolysis of skin targets |
EP1718366A4 (en) | 2004-02-06 | 2007-11-21 | Daniel Barolet | Method and device for the treatment of mammalian tissues |
US7344494B2 (en) | 2004-02-09 | 2008-03-18 | Karl Storz Development Corp. | Endoscope with variable direction of view module |
US6893259B1 (en) | 2004-03-08 | 2005-05-17 | Igor Reizenson | Oral hygiene device and method of use therefor |
JPWO2005092438A1 (en) | 2004-03-26 | 2008-05-22 | ヤーマン株式会社 | Treatment equipment |
WO2005096981A2 (en) | 2004-04-01 | 2005-10-20 | The General Hospital Corporation | Method and apparatus for dermatological treatment |
WO2005099369A2 (en) | 2004-04-09 | 2005-10-27 | Palomar Medical Technologies, Inc. | Emr treated islets |
US20090069741A1 (en) | 2004-04-09 | 2009-03-12 | Palomar Medical Technologies, Inc. | Methods And Devices For Fractional Ablation Of Tissue For Substance Delivery |
US20080132886A1 (en) | 2004-04-09 | 2008-06-05 | Palomar Medical Technologies, Inc. | Use of fractional emr technology on incisions and internal tissues |
US7842029B2 (en) | 2004-05-07 | 2010-11-30 | Aesthera | Apparatus and method having a cooling material and reduced pressure to treat biological external tissue |
WO2006006123A1 (en) | 2004-07-09 | 2006-01-19 | Koninklijke Philips Electronics N.V. | Light modulator |
US7333698B2 (en) | 2004-08-05 | 2008-02-19 | Polyoptics Ltd | Optical scanning device |
US20060047281A1 (en) | 2004-09-01 | 2006-03-02 | Syneron Medical Ltd. | Method and system for invasive skin treatment |
WO2006036968A2 (en) | 2004-09-28 | 2006-04-06 | Reliant Technologies, Inc. | Methods and apparatus for modulation of the immune response using light-based fractional treatment |
US20060094988A1 (en) | 2004-10-28 | 2006-05-04 | Tosaya Carol A | Ultrasonic apparatus and method for treating obesity or fat-deposits or for delivering cosmetic or other bodily therapy |
AU2005314712A1 (en) | 2004-12-09 | 2006-06-15 | Palomar Medical Technologies, Inc. | Oral appliance with heat transfer mechanism |
US7291141B2 (en) | 2005-02-02 | 2007-11-06 | Jay Harvey H | Method and apparatus for enhancing hair removal |
US7258695B2 (en) | 2005-02-08 | 2007-08-21 | Sonetics International | Hair restoration device and methods of using and manufacturing the same |
US20080183250A1 (en) | 2005-02-11 | 2008-07-31 | Hanafi Tanojo | Compositions and methods for treating or preventing skin inflammation via restoration of skin barrier function |
US20060253176A1 (en) | 2005-02-18 | 2006-11-09 | Palomar Medical Technologies, Inc. | Dermatological treatment device with deflector optic |
US20060271028A1 (en) | 2005-02-18 | 2006-11-30 | Palomar Medical Technologies, Inc. | Dermatological treatment device |
US20060217787A1 (en) | 2005-03-23 | 2006-09-28 | Eastman Kodak Company | Light therapy device |
US20080294150A1 (en) | 2005-04-01 | 2008-11-27 | Palomar Medical Technologies, Inc. | Photoselective Islets In Skin And Other Tissues |
US7856985B2 (en) | 2005-04-22 | 2010-12-28 | Cynosure, Inc. | Method of treatment body tissue using a non-uniform laser beam |
US7624640B2 (en) | 2005-06-03 | 2009-12-01 | Brown University | Opto-acoustic methods and apparatus for performing high resolution acoustic imaging and other sample probing and modification operations |
AU2006278255A1 (en) | 2005-08-08 | 2007-02-15 | Palomar Medical Technologies, Inc. | Eye-safe photocosmetic device |
AU2006279865B8 (en) | 2005-08-12 | 2013-01-31 | Board Of Regents, The University Of Texas System | Systems, devices, and methods for optically clearing tissue |
JP2009509140A (en) | 2005-09-15 | 2009-03-05 | パロマー・メデイカル・テクノロジーズ・インコーポレーテツド | Skin optical determination device |
US20070194717A1 (en) | 2006-02-17 | 2007-08-23 | Palomar Medical Technologies, Inc. | Lamp for use in a tissue treatment device |
US7727516B2 (en) | 2006-02-28 | 2010-06-01 | The Procter & Gamble Company | Reduction of hair growth |
EP1839705A1 (en) | 2006-03-27 | 2007-10-03 | Universidad de Alcala | Transcutaneous laser therapy patch |
US20070255355A1 (en) | 2006-04-06 | 2007-11-01 | Palomar Medical Technologies, Inc. | Apparatus and method for skin treatment with compression and decompression |
WO2007122611A2 (en) | 2006-04-20 | 2007-11-01 | Nano Pass Technologies Ltd. | Device and methods combining vibrating micro-protrusions with phototherapy |
US8136531B2 (en) | 2006-05-08 | 2012-03-20 | Chariff Mark D | Device and method for treating musculo-skeletal injury and pain by application of laser light therapy |
US8585707B2 (en) | 2006-06-07 | 2013-11-19 | Gary S. Rogers | Continuous low irradiance photodynamic therapy method |
JP2009542330A (en) | 2006-06-27 | 2009-12-03 | パロマー・メデイカル・テクノロジーズ・インコーポレーテツド | Handheld light beauty equipment |
US20080140164A1 (en) | 2006-12-06 | 2008-06-12 | Clrs Technology Corporation | Light emitting therapeutic devices and methods |
-
1999
- 1999-03-12 EP EP05076249A patent/EP1566149A1/en not_active Withdrawn
- 1999-03-12 ES ES99916129T patent/ES2245506T3/en not_active Expired - Lifetime
- 1999-03-12 US US09/268,433 patent/US6508813B1/en not_active Expired - Lifetime
- 1999-03-12 AU AU34507/99A patent/AU3450799A/en not_active Abandoned
- 1999-03-12 DE DE69926348T patent/DE69926348T2/en not_active Expired - Fee Related
- 1999-03-12 EP EP99916129A patent/EP1062001B1/en not_active Expired - Lifetime
- 1999-03-12 WO PCT/US1999/005501 patent/WO1999046005A1/en active IP Right Grant
- 1999-03-12 CA CA002323479A patent/CA2323479A1/en not_active Abandoned
-
2002
- 2002-09-17 US US10/245,825 patent/US6878144B2/en not_active Expired - Lifetime
-
2005
- 2005-03-30 US US11/093,693 patent/US7431719B2/en not_active Expired - Fee Related
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2008
- 2008-09-22 US US12/234,892 patent/US8328794B2/en not_active Expired - Fee Related
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US8328794B2 (en) | 2012-12-11 |
US6508813B1 (en) | 2003-01-21 |
DE69926348D1 (en) | 2005-09-01 |
EP1062001A1 (en) | 2000-12-27 |
US6878144B2 (en) | 2005-04-12 |
AU3450799A (en) | 1999-09-27 |
US7431719B2 (en) | 2008-10-07 |
WO1999046005A1 (en) | 1999-09-16 |
US20090137995A1 (en) | 2009-05-28 |
EP1566149A1 (en) | 2005-08-24 |
US20050171517A1 (en) | 2005-08-04 |
EP1062001B1 (en) | 2005-07-27 |
ES2245506T3 (en) | 2006-01-01 |
US20030065314A1 (en) | 2003-04-03 |
DE69926348T2 (en) | 2006-06-01 |
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EEER | Examination request | ||
FZDE | Discontinued |