CA2519304A1 - Rf electrode assembly for handpiece - Google Patents
Rf electrode assembly for handpiece Download PDFInfo
- Publication number
- CA2519304A1 CA2519304A1 CA002519304A CA2519304A CA2519304A1 CA 2519304 A1 CA2519304 A1 CA 2519304A1 CA 002519304 A CA002519304 A CA 002519304A CA 2519304 A CA2519304 A CA 2519304A CA 2519304 A1 CA2519304 A1 CA 2519304A1
- Authority
- CA
- Canada
- Prior art keywords
- electrode
- support structure
- coupled
- cooling member
- skin surface
- 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
Links
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- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
- A61H2201/10—Characteristics of apparatus not provided for in the preceding codes with further special therapeutic means, e.g. electrotherapy, magneto therapy or radiation therapy, chromo therapy, infrared or ultraviolet therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H7/00—Devices for suction-kneading massage; Devices for massaging the skin by rubbing or brushing not otherwise provided for
- A61H7/001—Devices for suction-kneading massage; Devices for massaging the skin by rubbing or brushing not otherwise provided for without substantial movement between the skin and the device
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H9/00—Pneumatic or hydraulic massage
- A61H9/005—Pneumatic massage
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H9/00—Pneumatic or hydraulic massage
- A61H9/005—Pneumatic massage
- A61H9/0071—Pneumatic massage by localized pressure, e.g. air streams or jets
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/36—General characteristics of the apparatus related to heating or cooling
- A61M2205/3606—General characteristics of the apparatus related to heating or cooling cooled
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0408—Use-related aspects
- A61N1/0452—Specially adapted for transcutaneous muscle stimulation [TMS]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N2005/0635—Radiation therapy using light characterised by the body area to be irradiated
- A61N2005/0643—Applicators, probes irradiating specific body areas in close proximity
- A61N2005/0645—Applicators worn by the patient
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Abstract
An RF device (10) has a support structure (18). An RF electrode (20), coupled to the support structure (18), includes conductive and dielectric portions. A
cooling member (22), coupled to the support structure, is configured to cool a back surface of the RF electrode (20). The cooling member (22) is distanced from the back surface of the RF electrode (20).
cooling member (22), coupled to the support structure, is configured to cool a back surface of the RF electrode (20). The cooling member (22) is distanced from the back surface of the RF electrode (20).
Description
RF ELECTRODE ASSEMBLY FOR HANDPIECE
BACKGROUND OF THE INVENTION
Field of the Invention This invention relates generally to an RF device, and more particularly to an RF
electrode that includes conductive and dielectric portions and is coupled to a support structure.
Description of Related Art The human skin is composed of two elements: the epidermis and the underlying dermis. The epidermis with the stratum corneum serves as a biological barrier to the environment. In the basilar layer of the epidermis, pigment-forming cells called melanocytes are present. They are the main determinants of skin color.
The underlying dermis provides the main structural support of the skin. It is composed mainly of an extra-cellular protein called collagen. Collagen is produced by fibroblasts and synthesised as a triple helix with three polypeptide chains that are connected with heat labile and heat stable chemical bonds. When collagen-containing tissue is heated, alterations in the physical properties of this protein matrix occur at a characteristic temperature. The structural transition of collagen contraction occurs at a specific "sln-inkage"
temperature. The shrinkage and remodeling of the collagen matrix with heat is the basis for the teclniology. Although the technology can be deployed to effect other changes to the skin, skin appendages (sweat glands, sebaceous glands, hair follicles, etc.), or subcutaneous tissue structures.
Collagen crosslinks are either intramolecular (covalent or hydrogen bond) or intermolecular (covalent or ionic bonds). The thermal cleavage of intramolecular hydrogen crosslinks is a scalar process that is created by the balance between cleavage events and relaxation events (reforming of hydrogen bonds). No external force is required for this process to occur. As a result, intermolecular stress is created by the thermal cleavage of intramolecular hydrogen bonds. Essentially, the contraction of the tertiary structure of the molecule creates the initial intermolecular vector of contraction.
Collagen fibrils in a matrix exhibit a variety of spatial orientations. The matrix is lengthened if the sum of all vectors acts to lengthen the fibril. Contraction of the matrix is facilitated if the sum of all extrinsic vectors acts to shorten the fibril.
Thermal disruption of intramolecular hydrogen bonds and mechanical cleavage of intermolecular crosslinks is also affected by relaxation events that restore preexisting configurations.
However, a permanent change of molecular length will occur if crosslinks are reformed after lengthening or contraction of the collagen fibril. The continuous application of an external mechanical force will increase the probability of crosslinks forming after lengthening or contraction of the fibril.
Hydrogen bond cleavage is a quantum mechanical event that requires a threshold of energy. The amount of (intramolecular) hydrogen bond cleavage required corresponds to the combined ionic and covalent intermolecular bond strengths within the collagen fibril. Until this threshold is reached, little or no change in the quaternary structure of the collagen fibril will occur. When the intermolecular stress is adequate, cleavage of the ionic and covalent bonds will occur. Typically, the intermolecular cleavage of ionic and covalent bonds will occur with a ratcheting effect from the realignment of polar and nonpolar regions in the lengthened or contracted fibril.
Cleavage of collagen bonds also occurs at lower temperatures but at a lower rate.
Low-level thermal cleavage is frequently associated with relaxation phenomena in which bonds are reformed without a net change in molecular length. An external force that mechanically cleaves the fibril will reduce the probability of relaxation phenomena and provides a means to lengthen or contract the collagen matrix at lower temperatures while reducing the potential of surface ablation.
Soft tissue remodeling is a biophysical phenomenon that occurs at cellular and molecular levels. lYlolecular contraction or partial denaturization of collagen involves the application of an energy source, which destabilizes the longitudinal axis of the molecule by cleaving the heat labile bonds of the triple helix. As a result, stress is created to break the intermolecular bonds of the matrix. This is essentially an immediate extra-cellular process, whereas cellular contraction requires a lag period for the migration and multiplication of fibroblasts into the wound as provided by the wound healing sequence. In higher developed animal species, the wound healing response to injury involves an initial inflammatory process that subsequently leads to the deposition of scar tissue.
The initial inflammatory response consists of the infiltration by white blood cells or leukocytes that dispose of cellular debris. Seventy-two hours later, proliferation of fibroblasts at the injured site occurs. These cells differentiate into contractile myofibroblasts, which are the source of cellular soft tissue contraction. Following cellular contraction, collagen is laid down as a static supporting matrix in the tightened soft tissue structure. The deposition and subsequent remodeling of this nascent scar matrix provides the means to alter the consistency and geometry of soft tissue for aesthetic purposes.
In light of the preceding discussion, there are a number of dermatological procedures that lend themselves to treatments which deliver thermal energy to the skin and underlying tissue to cause a contraction of collagen, and/or initiate a would healing response. Such procedures include skin remodeling/resurfacing, wrinkle removal, and treatment of the sebaceous glands, hair follicles adipose tissue and spider veins.
Currently available technologies that deliver thermal energy to the skin and underlying tissue include Radio Frequency (RF), optical (laser) and other forms of electromagnetic energy as well as ultrasound and direct heating with a hot surface. However, these technologies have a number of technical limitations and clinical issues which limit the effectiveness of the treatment and/or preclude treatment altogether.
These issues include the following: i) achieving a uniform thermal effect across a large area of tissue, ii) controlling the depth of the thermal effect to target selected tissue and prevent unwanted thermal damage to both target and non-target tissue, iii) reducing adverse tissue effects such as burns, redness blistering, iv) replacing the practice of delivery energy/treatment in a patchwork fashion with a more continuous delivery of treatment (e.g.
by a sliding or painting motion), v) improving access to difficult-to-reach areas of the skin surface and vi) reducing procedure time and number of patient visits required to complete treatment. hs will be discussed herein the current invention provides an apparatus for solving these and other limitations.
~ne of the key shortcomings of currently available RF technology for treating the skin is the edge effect phenomenon. In general, when RF energy is being applied or delivered to tissue through an electrode which is in contact with that tissue, the current concentrate around the edges of the electrode, sharp edges in particular. This effect is generally known as the edge effect. In the case of a circular disc electrode, the effect manifests as a higher current density around the perimeter of that circular disc and a relatively low current density in the center. For a square-shaped electrode there is typically a high current density around the entire perimeter, and an even higher current density at the corners.
Edge effects cause problems in treating the skin for several reasons. First, they result in a non-uniform thermal effect over the electrode surface. In various treatments of the skin, it is important to have a uniform thermal effect over a relatively large surface area, particularly for dermatological. treatments. Large in this case being on the order of several square millimeters or even several square centimeters. In electrosurgical applications for cutting tissue, there typically is a point type applicator designed with the goal of getting a hot spot at that point for cutting or even coagulating tissue. However, this point design is undesirable for creating a reasonably gentle thermal effect over a large surface area. What is needed is an electrode design to deliver uniform thermal energy to skin and underlying tissue without hot spots.
A uniform thermal effect is particularly important when cooling is combined with heating in skin/tissue treatment procedure. As is discussed below, a non-uniform thermal pattern makes cooling of the skin difficult and hence the resulting treatment process as well.
When heating the skin with RF energy, the tissue at the electrode surface tends to be warmest with a decrease in temperature moving deeper into the tissue. One approach to overcome tlus thermal gradient and create a thermal effect at a set distance away from the electrode is to cool the layers of skin that are in contact with the electrode. However, cooling of the skin is made difficult if there is a non-uniform heating pattern.
If the skin is sufficiently cooled such that there are no burns at the corners of a square or rectangular electrode, or at the perimeter of a circular disc electrode, then there will probably be ~vercooling in the center and there won't be any significant thermal effect (i.e.
tissue heating) under the center of the electrode. Contrarily, if the cooling effect is decreased to the point where there is a good thermal effect in the center of the electrode, then there probably will not be sufficient cooling to protect tissue in contact with the edges of the electrode. As a result of these 11n11tat1ons, in the typical application of a standard electrode there is usually an area of non-uniform treatment and/or burns on the skin surface. So uniformity of the heating pattern is very important. It is particularly important in applications treating skin where collagen-containing layers are heated to produce a collagen contraction response for tightening of the skin. For this and related applications, if the collagen contraction and resulting skin tightening effect are non-uniform, then a medically undesirable result may occur.
There is a need for an improved RF device. There is a further need for an RF
device that is suitable for cosmetic applications. There is a yet a further need for an RF device that utilizes an improved dielectric RF electrode.
SUMMARY OF THE INVENTION
Accordingly, an object of the present invention is to provide an improved RF
device.
BACKGROUND OF THE INVENTION
Field of the Invention This invention relates generally to an RF device, and more particularly to an RF
electrode that includes conductive and dielectric portions and is coupled to a support structure.
Description of Related Art The human skin is composed of two elements: the epidermis and the underlying dermis. The epidermis with the stratum corneum serves as a biological barrier to the environment. In the basilar layer of the epidermis, pigment-forming cells called melanocytes are present. They are the main determinants of skin color.
The underlying dermis provides the main structural support of the skin. It is composed mainly of an extra-cellular protein called collagen. Collagen is produced by fibroblasts and synthesised as a triple helix with three polypeptide chains that are connected with heat labile and heat stable chemical bonds. When collagen-containing tissue is heated, alterations in the physical properties of this protein matrix occur at a characteristic temperature. The structural transition of collagen contraction occurs at a specific "sln-inkage"
temperature. The shrinkage and remodeling of the collagen matrix with heat is the basis for the teclniology. Although the technology can be deployed to effect other changes to the skin, skin appendages (sweat glands, sebaceous glands, hair follicles, etc.), or subcutaneous tissue structures.
Collagen crosslinks are either intramolecular (covalent or hydrogen bond) or intermolecular (covalent or ionic bonds). The thermal cleavage of intramolecular hydrogen crosslinks is a scalar process that is created by the balance between cleavage events and relaxation events (reforming of hydrogen bonds). No external force is required for this process to occur. As a result, intermolecular stress is created by the thermal cleavage of intramolecular hydrogen bonds. Essentially, the contraction of the tertiary structure of the molecule creates the initial intermolecular vector of contraction.
Collagen fibrils in a matrix exhibit a variety of spatial orientations. The matrix is lengthened if the sum of all vectors acts to lengthen the fibril. Contraction of the matrix is facilitated if the sum of all extrinsic vectors acts to shorten the fibril.
Thermal disruption of intramolecular hydrogen bonds and mechanical cleavage of intermolecular crosslinks is also affected by relaxation events that restore preexisting configurations.
However, a permanent change of molecular length will occur if crosslinks are reformed after lengthening or contraction of the collagen fibril. The continuous application of an external mechanical force will increase the probability of crosslinks forming after lengthening or contraction of the fibril.
Hydrogen bond cleavage is a quantum mechanical event that requires a threshold of energy. The amount of (intramolecular) hydrogen bond cleavage required corresponds to the combined ionic and covalent intermolecular bond strengths within the collagen fibril. Until this threshold is reached, little or no change in the quaternary structure of the collagen fibril will occur. When the intermolecular stress is adequate, cleavage of the ionic and covalent bonds will occur. Typically, the intermolecular cleavage of ionic and covalent bonds will occur with a ratcheting effect from the realignment of polar and nonpolar regions in the lengthened or contracted fibril.
Cleavage of collagen bonds also occurs at lower temperatures but at a lower rate.
Low-level thermal cleavage is frequently associated with relaxation phenomena in which bonds are reformed without a net change in molecular length. An external force that mechanically cleaves the fibril will reduce the probability of relaxation phenomena and provides a means to lengthen or contract the collagen matrix at lower temperatures while reducing the potential of surface ablation.
Soft tissue remodeling is a biophysical phenomenon that occurs at cellular and molecular levels. lYlolecular contraction or partial denaturization of collagen involves the application of an energy source, which destabilizes the longitudinal axis of the molecule by cleaving the heat labile bonds of the triple helix. As a result, stress is created to break the intermolecular bonds of the matrix. This is essentially an immediate extra-cellular process, whereas cellular contraction requires a lag period for the migration and multiplication of fibroblasts into the wound as provided by the wound healing sequence. In higher developed animal species, the wound healing response to injury involves an initial inflammatory process that subsequently leads to the deposition of scar tissue.
The initial inflammatory response consists of the infiltration by white blood cells or leukocytes that dispose of cellular debris. Seventy-two hours later, proliferation of fibroblasts at the injured site occurs. These cells differentiate into contractile myofibroblasts, which are the source of cellular soft tissue contraction. Following cellular contraction, collagen is laid down as a static supporting matrix in the tightened soft tissue structure. The deposition and subsequent remodeling of this nascent scar matrix provides the means to alter the consistency and geometry of soft tissue for aesthetic purposes.
In light of the preceding discussion, there are a number of dermatological procedures that lend themselves to treatments which deliver thermal energy to the skin and underlying tissue to cause a contraction of collagen, and/or initiate a would healing response. Such procedures include skin remodeling/resurfacing, wrinkle removal, and treatment of the sebaceous glands, hair follicles adipose tissue and spider veins.
Currently available technologies that deliver thermal energy to the skin and underlying tissue include Radio Frequency (RF), optical (laser) and other forms of electromagnetic energy as well as ultrasound and direct heating with a hot surface. However, these technologies have a number of technical limitations and clinical issues which limit the effectiveness of the treatment and/or preclude treatment altogether.
These issues include the following: i) achieving a uniform thermal effect across a large area of tissue, ii) controlling the depth of the thermal effect to target selected tissue and prevent unwanted thermal damage to both target and non-target tissue, iii) reducing adverse tissue effects such as burns, redness blistering, iv) replacing the practice of delivery energy/treatment in a patchwork fashion with a more continuous delivery of treatment (e.g.
by a sliding or painting motion), v) improving access to difficult-to-reach areas of the skin surface and vi) reducing procedure time and number of patient visits required to complete treatment. hs will be discussed herein the current invention provides an apparatus for solving these and other limitations.
~ne of the key shortcomings of currently available RF technology for treating the skin is the edge effect phenomenon. In general, when RF energy is being applied or delivered to tissue through an electrode which is in contact with that tissue, the current concentrate around the edges of the electrode, sharp edges in particular. This effect is generally known as the edge effect. In the case of a circular disc electrode, the effect manifests as a higher current density around the perimeter of that circular disc and a relatively low current density in the center. For a square-shaped electrode there is typically a high current density around the entire perimeter, and an even higher current density at the corners.
Edge effects cause problems in treating the skin for several reasons. First, they result in a non-uniform thermal effect over the electrode surface. In various treatments of the skin, it is important to have a uniform thermal effect over a relatively large surface area, particularly for dermatological. treatments. Large in this case being on the order of several square millimeters or even several square centimeters. In electrosurgical applications for cutting tissue, there typically is a point type applicator designed with the goal of getting a hot spot at that point for cutting or even coagulating tissue. However, this point design is undesirable for creating a reasonably gentle thermal effect over a large surface area. What is needed is an electrode design to deliver uniform thermal energy to skin and underlying tissue without hot spots.
A uniform thermal effect is particularly important when cooling is combined with heating in skin/tissue treatment procedure. As is discussed below, a non-uniform thermal pattern makes cooling of the skin difficult and hence the resulting treatment process as well.
When heating the skin with RF energy, the tissue at the electrode surface tends to be warmest with a decrease in temperature moving deeper into the tissue. One approach to overcome tlus thermal gradient and create a thermal effect at a set distance away from the electrode is to cool the layers of skin that are in contact with the electrode. However, cooling of the skin is made difficult if there is a non-uniform heating pattern.
If the skin is sufficiently cooled such that there are no burns at the corners of a square or rectangular electrode, or at the perimeter of a circular disc electrode, then there will probably be ~vercooling in the center and there won't be any significant thermal effect (i.e.
tissue heating) under the center of the electrode. Contrarily, if the cooling effect is decreased to the point where there is a good thermal effect in the center of the electrode, then there probably will not be sufficient cooling to protect tissue in contact with the edges of the electrode. As a result of these 11n11tat1ons, in the typical application of a standard electrode there is usually an area of non-uniform treatment and/or burns on the skin surface. So uniformity of the heating pattern is very important. It is particularly important in applications treating skin where collagen-containing layers are heated to produce a collagen contraction response for tightening of the skin. For this and related applications, if the collagen contraction and resulting skin tightening effect are non-uniform, then a medically undesirable result may occur.
There is a need for an improved RF device. There is a further need for an RF
device that is suitable for cosmetic applications. There is a yet a further need for an RF device that utilizes an improved dielectric RF electrode.
SUMMARY OF THE INVENTION
Accordingly, an object of the present invention is to provide an improved RF
device.
Another object of the present invention is to provide an RF device that includes an RF
electrode conductive and dielectric portions.
Yet another object of the present invention is to provide an a di-electric RF
electrode coupled to a support member.
These and other objects of the present invention are achieved in an RF device with a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. A cooling member, coupled to the support structure, is configured to cool a back surface of the RF electrode. The cooling member is distanced from the back surface of the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions and a flex circuit. A cooling member, coupled to the support structure, is configured to cool a back surface of the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, has conductive and dielectric portions. First and second engagement members are formed in the body of the support structure. The first and second engagement members provide engagement and disengagement with a handpiece support structure.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, including conductive and dielectric portions, is configured to be capacitively coupled when at least a portion of the 12F electrode is in contact with a skin surface. A back plate is positioned at a proximal portion of the support structure. A plurality of electrical contact pads is coupled to the back plate.
In another embodiment of the present invention, an 12F device includes a support structure. An RF electrode includes conductive and dielectric portions, a tissue interface surface and an opposing back surface. A back plate is positioned at a proximal portion of the support structure. The back plate includes a front surface that faces the opposing back surface of the RF electrode, and an opposing back surface. A cooling member is provided with a channel that has a distal section extending through the back plate, and a proximal section that is raised above the back surface of the back plate.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface and an opposing back surface. A cooling member is coupled to the support structure. At least a first sensor is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface and an opposing back surface. A cooling member is coupled to the support structure. A non-volatile memory is coupled to the support structure.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, has conductive and dielectric portions. A cooling member coupled to the support structure is configured to cool a back surface of the RF electrode. The cooling member is distanced from the back surface of the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure defining a body of an I~F device. An RF electrode is provided that has conductive and dielectric portions. The RF electrode includes a flex circuit. A cooling member, coupled to the support structua-e, is configured to cool a back surface of the RF
electrode.
In another embodiment of the present invention, an ~F° device includes a support structure. An I~F electrode, coupled to the support structure, includes conductive and dielectric portions. First and second engagement members are formed in the body of the support structure. The first and second engagement members provide engagement and disengagement with a handpiece support structure.
W another embodiment of the present invention, an I~F device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The I~F electrode is configured to be capacativly coupled when at least a portion of the RF electrode is in contact with a skin surface. A back plate is positioned at a proximal portion of the support structure. A plurality of electrical contact pads is coupled to the back plate.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions, a tissue interface surface and an opposing back surface.
A back plate is positioned at a proximal portion of the support structure. The back plate includes a front surface that faces the opposing back surface of the RF electrode and an opposing back surface. A cooling member has a channel with a distal section that extends through the back plate, and a proximal section that is raised above the back surface of the back plate.
electrode conductive and dielectric portions.
Yet another object of the present invention is to provide an a di-electric RF
electrode coupled to a support member.
These and other objects of the present invention are achieved in an RF device with a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. A cooling member, coupled to the support structure, is configured to cool a back surface of the RF electrode. The cooling member is distanced from the back surface of the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions and a flex circuit. A cooling member, coupled to the support structure, is configured to cool a back surface of the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, has conductive and dielectric portions. First and second engagement members are formed in the body of the support structure. The first and second engagement members provide engagement and disengagement with a handpiece support structure.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, including conductive and dielectric portions, is configured to be capacitively coupled when at least a portion of the 12F electrode is in contact with a skin surface. A back plate is positioned at a proximal portion of the support structure. A plurality of electrical contact pads is coupled to the back plate.
In another embodiment of the present invention, an 12F device includes a support structure. An RF electrode includes conductive and dielectric portions, a tissue interface surface and an opposing back surface. A back plate is positioned at a proximal portion of the support structure. The back plate includes a front surface that faces the opposing back surface of the RF electrode, and an opposing back surface. A cooling member is provided with a channel that has a distal section extending through the back plate, and a proximal section that is raised above the back surface of the back plate.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface and an opposing back surface. A cooling member is coupled to the support structure. At least a first sensor is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface and an opposing back surface. A cooling member is coupled to the support structure. A non-volatile memory is coupled to the support structure.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, has conductive and dielectric portions. A cooling member coupled to the support structure is configured to cool a back surface of the RF electrode. The cooling member is distanced from the back surface of the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure defining a body of an I~F device. An RF electrode is provided that has conductive and dielectric portions. The RF electrode includes a flex circuit. A cooling member, coupled to the support structua-e, is configured to cool a back surface of the RF
electrode.
In another embodiment of the present invention, an ~F° device includes a support structure. An I~F electrode, coupled to the support structure, includes conductive and dielectric portions. First and second engagement members are formed in the body of the support structure. The first and second engagement members provide engagement and disengagement with a handpiece support structure.
W another embodiment of the present invention, an I~F device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The I~F electrode is configured to be capacativly coupled when at least a portion of the RF electrode is in contact with a skin surface. A back plate is positioned at a proximal portion of the support structure. A plurality of electrical contact pads is coupled to the back plate.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions, a tissue interface surface and an opposing back surface.
A back plate is positioned at a proximal portion of the support structure. The back plate includes a front surface that faces the opposing back surface of the RF electrode and an opposing back surface. A cooling member has a channel with a distal section that extends through the back plate, and a proximal section that is raised above the back surface of the back plate.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface and an opposing back surface. A cooling member is coupled to the support structure. At least a first sensor is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface and an opposing back surface. A cooling member is coupled to the support structure. A non-volatile memory is coupled to the support structure.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface, an opposing back surface and an outer edge with a geometry configured to reduce an amount of capacitively coupled area at the outer edge.
In another embodiment of the present invention, an l~F device includes a support structure. An I~ electrode, coupled to the support structure, includes conductive and dielectric portions. The IZF' electrode has a tissue interface surface and an opposing back surface. At least a portion of the RF electrode has voids that reduce an amount of conductive material in the RF electrode.
In another embodiment of the present invention, an I~F' device includes a support structure. An RF electrode, coupled to the suppout structure, includes conductive and dielectric portions. The RF electrode is configured to provide a controllable tissue effect on subcutaneous tissue while preserving an epidermal skin surface overlying the subcutaneous tissue.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode is coupled to the support structure. A flex circuit is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure, an RF electrode and a flex circuit coupled to the RF electrode. A
plurality of electrical contact pads is coupled to the flex circuit.
In another embodiment of the present invention, an RF device includes a support structure An RF electrode, coupled to the support structure, includes conductive and dielectric portions. A plurality of electrical contact pads is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface and an opposing back surface. A cooling member is coupled to the support structure. A non-volatile memory is coupled to the support structure.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. The RF electrode has a tissue interface surface, an opposing back surface and an outer edge with a geometry configured to reduce an amount of capacitively coupled area at the outer edge.
In another embodiment of the present invention, an l~F device includes a support structure. An I~ electrode, coupled to the support structure, includes conductive and dielectric portions. The IZF' electrode has a tissue interface surface and an opposing back surface. At least a portion of the RF electrode has voids that reduce an amount of conductive material in the RF electrode.
In another embodiment of the present invention, an I~F' device includes a support structure. An RF electrode, coupled to the suppout structure, includes conductive and dielectric portions. The RF electrode is configured to provide a controllable tissue effect on subcutaneous tissue while preserving an epidermal skin surface overlying the subcutaneous tissue.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode is coupled to the support structure. A flex circuit is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure, an RF electrode and a flex circuit coupled to the RF electrode. A
plurality of electrical contact pads is coupled to the flex circuit.
In another embodiment of the present invention, an RF device includes a support structure An RF electrode, coupled to the support structure, includes conductive and dielectric portions. A plurality of electrical contact pads is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. At least portions of the RF electrode have different widths.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. At least portions of the RF electrode have different conductivities.
In another embodiment of the present invention, an RF device includes an RF
electrode with conductive and dielectric portions. A support structure is coupled to the RF
electrode. The support structure and the RF electrode form a seal where the support structure is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes an RF
electrode with conductive and dielectric portions. A support structure is coupled to the RF
electrode. A cooling member, coupled to the support structure, is configured to deliver cool a back surface of the RF electrode. The cooling member is distanced from the back surface of the RF electrode. The support structure and the RF electrode form a seal where the support structure is coupled to the I~F electrode.
EI~IEF I~ESCI~IPTI~~T ~F THE DI~AWII~CaS
Figure 1(a) is a cross-sectional view of one embodiment of the handpiece of the present invention.
Figure 1 (b) is a cross-sectional view of another embodiment of the RF device with a thermoelectric cooler.
Figure 2 is an exploded view of the Figure 1 RF electrode assembly.
Figure 3(a) is a close-up view of one embodiment of an RF electrode of the present invention.
Figure 3(b) illustrates one embodiment of an RF electrode, that can be utilized with the present invention, with an outer edge geometry configured to reduce an amount of capacitively coupled area the outer edge.
Figure 3(c) illustrates an one embodiment of an RF electrode, that can be utilized with the present invention, that has voids where there is little if any conductive material.
Figure 4 is a cross-sectional view of the RF electrode assembly from Figure 1.
Figure 5 is a side view of one embodiment of an RF handpiece assembly of the present invention.
Figure 6 is a rear view of the Figure 5 RF electrode assembly.
DETAILED DESCRIPTION
In various embodiments, the present invention provides methods for treating a tissue site. In one embodiment, an energy delivery surface of an energy delivery device is coupled to a skin surface. The coupling can be a direct, in contact, placement of the energy delivery surface of the energy delivery on the skin surface, or distanced relationship between the two with our without a media to conduct energy to the skin surface from the energy delivery surface of the energy delivery device. The skin surface is cooled sufficiently to create a reverse thermal gradient where a temperature of the skin surface is less than an underlying tissue. Energy is delivered from the energy delivery device to the underlying tissue area, resulting in a tissue effect at the skin surface.
Referring now to Figure 1 (a), the methods of present invention can be achieved with the use of a handpiece 10. Handpiece 10 is coupled with a handpiece assembly 12 that includes a handpiece housing 14 and a cooling fluitlic medium valve member 16.
Handpiece housing 14 is configured to be coupled to an electrode assembly 18. Electrode assembly 18 has a least one RF electrode 20 that is capacitively coupled to a skin surface when at least a portion of RF electrode 20 is in contact with the skin surface. Without limiting the scope of the present invention, RF electrode 20 can have a thickness in the range of 0.010 to 1.0 mm.
Handpiece 10 provides a more uniform thermal effect in tissue at a selected depth, while preventing or minimizing thermal damage to the skin surface and other non-target tissue. Handpiece 10 is coupled to an RF generator. RF electrode 20 can be operated either in mono-polar or bi-polar modes. Handpiece 10 is configured to reduce, or preferably eliminate edge effects and hot spots. The result is an improved aesthetic result/clinical outcome with an elimination/reduction in adverse effects and healing time.
A fluid delivery member 22 is coupled to cooling fluitlic medium valve member 16.
Fluid delivery member 22 and cooling fluitlic medium valve member 16 collectively form a cooling fluitlic medium dispensing assembly. Fluid delivery member 22 is configured to provide an atomizing delivery of a cooling fluitlic medium to RF electrode 20.
The atomizing delivery is a mist or fine spray. A phase transition, from liquid to gas, of the cooling fluitlic medium occurs when it hits the surface of RF electrode 20.
The transition from liquid to gas creates the cooling. If the transition before the cooling fluitlic medium hits RF electrode 20 the cooling of RF electrode 20 will not be as effective.
In another embodiment, illustrated in Figure 1(b), a thermo-electric cooler 23 is utilized in place of cooling fluitlic medium valve member 16 and fluid delivery member 22.
In one embodiment, the cooling fluitlic medium is a cryogenic spray, commercially available from Honeywell, Morristown, New Jersey. A specific example of a suitable cryogenic spray is R134A2, available from Refron, Inc., 38-18 33rd St" Long Island City, New York 11101. The use of a cryogenic cooling fluitlic medium provides the capability to use a number of different types of algorithms for skin treatment. For example, the cryogenic cooling fluitlic medium can be applied milliseconds before and after the delivery of RF
energy to the desired tissue. This is achieved with the use of cooling fluitlic medium valve member 16 coupled to a cryogen supply, including but not limited to a compressed gas canister. In various embodiments, cooling fluitlic medium valve member 16 can be coupled to a computer control system and/or manually controlled by the physician by means of a foot switch or similar device.
Providing a spray, or atomization, of cryogenic cooling fluitlic medium is particularly suitable because of it provides an availability to implement rapid on and off control.
Cryogenic cooling fluitlic medium allows more precise temporal control of the cooling process. This is because cooling only occurs when the refrigerant is sprayed and is in an evaporative state, the latter being a very fast short-lived event. Thus, cooling ceases rapidly after the cryogenic cooling fluitlic medium is stopped. The overall effect is to confer very precise time on-off control of cryogenic cooling fluitlic medium.
Referring now to Figure 2, fluid delivery member 22 and thenno-electric cooler can be positioned in handpiece housing 14 or electrode assembly 18. Fluid delivery member 22 is configured to controllably deliver a cooling fluitlic medium. Fluid delivery member 22 and thermo-electric cooler 23 cool a back surface 24 of RF electrode 20 and maintain back surface 24 at a desired temperature. The cooling fluitlic medium evaporatively cools RF
electrode 20 and maintains a substantially uniform temperature of front surface 26 of RF
electrode 20. Fluid delivery member 22 evaporatively cools baclc surface 24.
Front surface 26 may or may not be flexible and conformable to the skin, but it will still have sufficient strength and/or structure to provide good thermal coupling when pressed against the skin surface.
RF electrode 20 then conductively cools a skin surface that is adj acent to a front surface 26 of RF electrode 20. Suitable fluidic media include a variety of refrigerants such as R134A and freon.
Fluid delivery member 22 is configured to controllably deliver the cooling fluidic medium to back surface 24 at substantially any orientation of front surface 26 relative to a direction of gravity. A geometry and positioning of fluid delivery member 22 is selected to provide a substantially uniform distribution of cooling fluidic medium on back surface 24.
The delivery of the cooling fluidic medium can be by spray of droplets or fine mist, flooding back surface 24, and the like. Cooling occurs at the interface of the cooling fluidic medium with atmosphere, which is where evaporation occurs. If there is a thick layer of fluid on back surface 24 the heat removed from the treated skin will need to pass through the thick layer of cooling fluidic medium, increasing thermal resistance. To maximize cooling rates, it is desirable to apply a very thin layer of cooling fluidic medium. If RF
electrode 20 is not horizontal, and if there is a thick layer of cooling fluitlic medium, or if there are large drops of cooling fluitlic medium on back surface 24 , the cooling fluitlic medium can run down the surface of RF electrode 20 and pool at one edge or corner, causing uneven cooling.
Therefore, it is desirable to apply a thin layer of cooling fluitlic medium with a fine spray.
Thernio-electric cooler 23 achieves these same results but without delivering a cooling medium. Thermo-electric cooler 23 is cold on the side that is adjacent to or in contact with surface 24, while its opposing side becomes wanner.
In various embodiments, RF electrode 20, as illustrated in Figure 3(a), has a conductive portion 28 and a dielectric portion 30. Conductive portion 28 can be a metal including but not limited to copper, gold, silver, aluminum and the like.
Dielectric portion 30 can be made of a variety of different materials including but not limited to polyimide, Teflon~ and the lilce, silicon nitride, polysilanes, polysilazanes, polyimides, I~apton and other polymers, antenna dielectrics and other dielectric materials well known in the art. Other dielectric materials include but are not limited to polymers such as polyester, silicon, sapphire, diamond, zirconium-toughened alumina (ZTA), alumina and the like.
Dielectric portion 30 can be positioned around at least a portion, or the entirety of a periphery of conductive portion 28. In another embodiment, RF electrode 20 is made of a composite material, including but not limited to gold-plated copper, copper-polyimide, silicon/silicon-nitride and the like.
Dielectric portion 30 creates an increased impedance to the flow of electrical current through RF electrode 20. This increased impedance causes current to travel a path straight down through conductive portion 28 to the skin surface. Electric field edge effects, caused by a concentration of current flowing out of the edges of RF electrode 20, are reduced.
Dielectric portion 30 produces a more uniform impedance through RF electrode and causes a more uniform current to flow through conductive portion 28. The resulting effect minimizes or even eliminates, edge effects around the edges of RF
electrode 20. As shown in Figure 3(c), RF electrode 20 can have voids 33 where there is little or no conductive material. Creating voids 33 in the conductive material alters the electric field. The specific configuration of voids can be used to minimize edge effect, or alter the depth, uniformity or shape of the electric field. Under a portion 28'of the RF electrode 20 with solid conductive material the electric field is deeper. Under a portion 28"of RF electrode 20 with more voids, the electric field is shallower. By combining different densities of conductive material, an RF
electrode 20 is provided to match the desired heating profile.
In one embodiment, conductive portion 28 adheres to dielectric portion 30 which can be a substrate with a thickness, by way of example and without limitation, of about 0.001".
This embodiment is similar to a standard flex circuit board material commercially available in the electronics industry. In this embodiment, dielectric pot-tion 30 is in contact with the tissue, the skin, and conductive portion 28 is separated from the skin.
The thickness of the dielectric portion 30 can be decreased by growing conductive portion 28 on dielectric portion 30 using a variety of techniques, including but not limited to, sputtering, electro deposition, chemical vapor deposition, plasma deposition and other deposition teclmiques known in the art. Additionally, these same processes can be used to deposit dielectric portion 30 onto conductive portion 28. In one embodiment dielectric portion 30 is an oxide layer which can be grown on conductive portion 28. An oxide layer has a low thernlal resistance and improves the cooling efficiency of the skin compared with many other dielectrics such as polymers.
In various embodiments, RF electrode 20 is configured to inhibit the capacitive coupling to tissue along its outside edge 31. Referring to Figure 3(b) RF
electrode 20 can have an outer edge 31 with a geometry that is configured to reduce an amount of capacitively coupled area at outer edge 31. Outer edge 31 can have less of the conductive portion 28 material. This can be achieved by different geometries, including but not limited to a scalloped geometry, and the like. The total length of outer edge 31 can be increased, with different geometries, and the total area that is capacitively coupled to tissue is reduced. This produces a reduction in energy generation around outer edge 31.
Alternatively, the dielectric material can be applied in a thicker layer at the edges, reducing the electric field at the edges. A further alternative is to configure the cooling to cool more aggressively at the edges to compensate for any electric field edge effect.
Fluid delivery member 22 has an inlet 32 and an outlet 34. Outlet 34 can have a smaller cross-sectional area than a cross-sectional area of inlet 32. In one embodiment, fluid delivery member 22 is a nozzle 36.
Cooling fluidic medium valve member 16 can be configured to provide a pulsed delivery of the cooling fluidic medium. Pulsing the delivery of cooling fluidic medium is a simple way to control the rate of cooling fluidic medium application. In one embodiment, cooling fluidic medium valve member 16 is a solenoid valve. An example of a suitable solenoid valve is a solenoid pinch valve manufactured by the N-Research Corporation, West Caldwell, NJ. If the fluid is pressurized, then opening of the valve results in fluid flow. If the fluid is maintained at a constant pressure, then the flow rate is constant and a simple open/close solenoid valve can be used, the effective flow rate being determined by the pulse duty cycle. A higher duty cycle, close to 100°/~ increases cooling, while a lower duty cycle, closer to 0%, reduces cooling. The duty cycle can be achieved by turning on the valve for a short duration of time at a set frequency. The duration of the open time can be 1 to 50 milliseconds or longer. The frequency of pulsing can be 1 to 50 I-Iz or faster.
Alternatively, cooling fluidic medium flow rate can be controlled by a metering valve or controllable-rate pump such as a peristaltic pump. One advantage of pulsing is that it is easy to control using simple electronics and control algorithms.
Electrode assembly 18 is sufficiently sealed so that the cooling fluidic medium does not leak from back surface 24 onto a skin surface in contact with a front surface of RF
electrode 20. This helps provide an even energy delivery through the skin surface. In one embodiment, electrode assembly 18, and more specifically RF electrode 20, has a geometry that creates a reservoir at back surface 24 to hold and gather cooling fluidic medium that has collected at back surface 24. Back surface 24 can be formed with "hospital corners" to create this reservoir. Optionally, electrode assembly 18 includes a vent that permits vaporized cooling fluidic medium to escape from electrode assembly 18.
The vent prevents pressure from building up in electrode assembly 18. The vent can be a pressure relief valve that is vented to the atmosphere or a vent line.
When the cooling fluidic medium comes into contact with RF electrode 20 and evaporates, the resulting gas pressurizes the inside of electrode assembly 18. This can cause RF electrode 20 to partially inflate and bow out from front surface 26. The inflated RF electrode 20 can enhance the thermal contact with the skin and also result in some degree of conformance of RF electrode 20 to the skin surface. An electronic controller can be provided. The electronic controller sends a signal to open the vent when a programmed pressure has been reached.
Various leads 40 are coupled to RF electrode 20. One or more thermal sensors 42 are coupled to RF electrode. Suitable thermal sensors 42 include but are not limited to thermocouples, thermistors, infrared photo-emitters and a thermally sensitive diode. In one embodiment, a thermal sensor 42 is positioned at each corner of RF electrode 20. A sufficient number of thermal sensors 42 are provided in order to acquire sufficient thermal data of the skin surface or the back surface 24 of the electrode 20. Thermal sensors 42 are electrically isolated from RF electrode 20. In another embodiment, at least one sensor 42 is positioned at baclc surface 24 of RF electrode and detects the temperature of back surface 24 in response to the delivery of cooling fluidic medium.
Thermal sensors 4.2 measure temperature and can provide feedback for monitoring temperature of RF electrode 20 and/or the tissue during treatment.. Thermal sensors 42 can be thermistors, thermocouples, thermally sensitive diodes, capacitors, inductors or other devices for measuring temperature. Preferably, thermal sensors 4.2 provide electronic feedback to a microprocessor of the RF generator coupled to RF°
electrode 20 in order to facilitate control of the treatment.
Measurements from thermal sensors 42 can be used to help control the rate of application of cooling fluitlic medium. For example, a cooling control algoritlun can be used to apply cooling fluitlic medium to RF electrode 20 at a high flow rate until the temperature fell below a target temperature, and then slow down or stop. A PID, or proportional-integral-differential, algorithm can be used to precisely control RF electrode 20 temperature to a predetermined value.
Thermal sensors 42 can be positioned on back surface 24 of RF electrode 20 away from the tissue. This configuration is preferable for controlling the temperature of the RF
electrode 20. Alternatively, thermal sensors 42 can be positioned on front surface 26 of RF
electrode 10 in direct contact with the tissue. This embodiment can be more suitable for monitoring tissue temperature. Algorithms are utilized with thermal sensors 42 to calculate a temperature profile of the treated tissue. Thermal sensors 42 can be used to develop a temperature profile of the skin which is then used for process control purposes to assure that the proper amounts of heating and cooling are delivered to achieve a desired elevated deep , tissue temperature while maintaining skin tissue layers below a threshold temperature and avoid thermal injury.
The physician can use the measured temperature profile to assure that he stays within the boundary of an ideal/average profile for a given type of treatment.
Thermal sensors 42 can be used for additional purposes. When the temperature of thermal sensors 42 is monitored it is possible to detect when RF electrode 20 is in contact with the skin surface.
This can be achieved by detecting a direct change in temperature when skin contact is made or examining the rate of change of temperature which is affected by contact with the skin.
Similarly, if there is more than one thermal sensor 42, the thermal sensors 42 can be used to detect whether a portion of RF electrode 20 is lifted or out of contact with skin. This can be important because the current density (amperes per unit area) delivered to the skin can vary if the contact area changes. In particular, if part of the surface of RF
electrode 20 is not in contact with the skin, the resulting current density is higher than expected.
Deferring again to Figure 1(a), a force sensor 44 is also coupled to electrode assembly 1 ~. Force sensor 44~ detects an amount of force applied by electrode assembly 1 S, via the physician, against an applied skin surface. Force sensor 44 zeros out gravity effects of the weight of electrode assembly 1 ~ in any orientation of front surface 26 of RF
electrode 20 relative to a direction of gravity. Additionally, force sensor 44 provides an indication when DF electrode 20 is in contact with a skin surface. Force sensor 44 also provides a signal indicating that a force applied by DF electrode 20 to a contacted skin surface is, (i) above a minimum threshold or (ii) below a maximum threshold.
As illustrated in Figure 4, an activation button 46 is used in conjunction with the force sensor. Just prior to activating DF electrode 20, the physician holds handpiece 10 in position just off the surface of the slcin. The orientation of handpiece 10 can be any angle relative to the direction of gravity. To arm handpiece 10, the physician can press activation button 46 which tares force sensor 44, by setting it to read zero. This cancels the force due to gravity in that particular treatment orientation. This method allows consistent force application of RF
electrode 20 to the skin surface regardless of the angle of handpiece 10 relative to the direction of gravity.
RF electrode 20 can be a flex circuit, which can include trace components.
Additionally, thermal sensor 42 and force sensor 44 can be part of the flex circuit. Further, the flex circuit can include a dielectric that forms a part of RF electrode 20.
Electrode assembly 18 can be moveably positioned within handpiece housing 12.
In one embodiment, electrode assembly 18 is slideably moveable along a longitudinal axis of handpiece housing 12.
Electrode assembly 18 can be rotatably mounted in handpiece housing 12.
Additionally, RF electrode 20 can be rotatably positioned in electrode assembly 18.
Electrode assembly 18 can be removably coupled to handpiece housing 12 as a disposable or non-disposable RF device 52.
For purposes of this disclosure, electrode assembly 18 is the same as RF
device 52.
Qnce movably mounted to handpiece housing 12, RF device 52 can be coupled to handpiece housing 12 via force sensor 44. Force sensor 44 can be of the type that is capable of measuring both compressive and tensile forces. In other embodiments, force sensor 44 only measures compressive forces, or only measures tensile forces.
RF device 52 can be spring-loaded with a spring 48. In one embodiment, spring biases RF electrode 20 in a direction toward handpiece housing 12. This pre-loads force sensor 44 and keeps RF device 52 pressed against force sensor 44.. The pre-load force is tared when activation button 46 is pressed just prior to application of RF
electrode 20 to the skin surface.
A shroud 50 is optionally coupled to handpiece 10. Shroud 50 serves to keep the user from touching RF device 52 during use which can cause erroneous force readings.
A non-volatile memory 54 can be included with RF device 52. Additionally, non-volatile memory can be included with handpiece housing 12. Non-volatile memory 54 can be an EPR~M and the like. Additionally, a second non-volatile memory can be included in handpiece housing 12 for purposes of storing handpiece 10 information such as but not limited to, handpiece model number or version, handpiece software version, number of RF
applications that handpiece 10 has delivered, expiration date and manufacture date.
Handpiece housing 12 can also contain a microprocessor 58 for purposes of acquiring and analyzing data from various sensors on handpiece housing 12 or RF device 52 including but not limited to thermal sensors 42 , force sensors 44, fluid pressure gauges, switches, buttons and the like.
Microprocessor 58 can also control components on handpiece 10 including but not limited to lights, LEDs, valves, pumps or other electronic components.
Microprocessor 58 can also communicate data to a microprocessor of the RF generator.
Non-volatile memory 54 can store a variety of data that can facilitate control and operation of handpiece 10 and its associated system including but not limited to, (i) controlling the amount of current delivered by RF electrode 20, (ii) controlling the duty cycle of the fluid delivery member 22 and thermo-electric cooler 23, (iii) controlling the energy delivery duration time of the RF electrode 20, (iv) controlling the temperature of RF electrode 20 relative to a target temperature, (v) providing a maximum number of firings of RF
electrode 20, (vi) providing a maximum allowed voltage that is deliverable by RF electrode 20, (vii) providing a history of RF electrode 20 use, (viii) providing a controllable duty cycle to fluid delivery member 22 and thermo-electric cooler 23 for the delivery of the cooling fluidic medium to back surface 24 of RF electrode 20, (ix) providing a controllable delivery rate of cooling fluidic medium delivered from fluid delivery member 22 to back surface 24, (x) providing a control of thermo-electric cooler 23 and the like.
F~eferring now to Figures 5 and 6, FtF device 52 includes a support structure, including but not limited to a housing 60 that defines the body of I~F device 52. 1tF
device 52 can include a baclc plate 62 that is positioned at a proximal portion of support structure 60. A
plurality of electrical contact pads 64 can be positioned at back plate 62. At least a portion of fluid delivery member 22 and thermo-electric cooler 23 can extend through back plate 62.
Fluid delivery nlenlber 22 can be a channel with a proximal end that is raised above the back surface of back plate 62.
First and second engagement members 64 can also be formed in the body of support structure 60. Engagement members 64 provide engagement and disengagement with handpiece housing 14. Suitable engagement members 64 include but are not limited to snap members, apertures to engage with snap members of substrate support 60, and the like.
Handpiece 10 can be used to deliver thermal energy to modify tissue including, but not limited to, collagen containing tissue, in the epidermal, dermal and subcutaneous tissue layers, including adipose tissue. The modification of the tissue includes modifying a physical feature of the tissue, a structure of the tissue or a physical property of the tissue. The modification can be achieved by delivering sufficient energy to modify collagen containing tissue, cause collagen shrinkage, and/or a wound healing response including the deposition of new or nascent collagen, and the like.
Handpiece 10 can be utilized for performing a number of treatments of the skin and underlying tissue including but not limited to, (i) dermal remodeling and tightening, (ii) wrinkle reduction, (iii) elastosis reduction, (iv) scar reduction, (v) sebaceous gland removal/deactivation and reduction of activity of sebaceous gland, (vi) hair follicle removal, (vii) adipose tissue remodeling/removal, (viii) spider vein removal, (ix) modify contour irregularities of a skin surface, (x) create scar or nascent collagen, (xi) reduction of bacteria activity of skin, (xii) reduction of skin pore size, (xiii) unclog skin pores and the like.
In various embodiments, handpiece 10 can be utilized in a variety of treatment processes, including but not limited to, (i) pre-cooling, before the delivery of energy to the tissue has begun, (ii) an on phase or energy delivery phase in conjunction with cooling and (iii) post cooling after the delivery of energy to tissue has stopped.
Handpiece 10 can be used to pre-cool the surface layers of the target tissue so that when RF electrode 20 is in contact with the tissue, or prior to turning on the RF energy source, the superficial layers of the target tissue are already cooled. When RF energy source is turned on or delivery of RF to the tissue otherwise begins, resulting in heating of the tissues, the tissue that has been cooled is protected from thermal effects including thermal damage. The tissue that has not been cooled will warm up to therapeutic temperatures resulting in the desired therapeutic effect.
Pre-cooling gives time for the thermal effects of cooling to propagate down into the tissue. More specifically, pre-cooling allows the achievement of a desired tissue depth thermal profile, with a minimum desired temperature being achieved at a selectable depth.
The amount or duration of pre-cooling can be used to select the depth of the protected zone of untreated tissue. Longer durations of pre-cooling produce a deeper protected zone and hence a deeper level in tissue for the start of the treatment zone. The opposite is true for shorter periods of pre-cooling. The temperature of front surface 26 of hF electrode 20 also affects the temperature profile. The colder the temperature of front surface 26, the faster and deeper the cooling, and vice verse.
Post-cooling can be important because it prevents and/or reduces heat delivered to the deeper layers from conducting upward and heating the more superficial layers possibly to therapeutic or damaging temperature range even though external energy delivery to the tissue has ceased. In order to prevent this and related thermal phenomena, it can be desirable to maintain cooling of the treatment surface for a period of time after application of the RF
energy has ceased. In various embodiments, varying amounts of post cooling can be combined with real-time cooling and/or pre-cooling.
In various embodiments, handpiece 10 can be used in a varied number of pulse on-off type cooling sequences and algorithms may be employed. In one embodiment, the treatment algorithm provides for pre-cooling of the tissue by starting a spray of cryogenic cooling fluidic medium, followed by a short pulse of RF energy into the tissue. In this embodiment, the spray of cryogenic cooling fluidic medium continues while the RF energy is delivered, and is stopping shortly thereafter, e.g. on the order of milliseconds. This or another treatment sequence can be repeated again. Thus in various embodiments, the treatment sequence can include a pulsed sequence of cooling on, heat, cooling off, cooling on, heat, cool off, and with cooling and heating durations on orders of tens of milliseconds. In these embodiments, every time the surface of the tissue of the skin is cooled, heat is removed from the skin surface.
Cryogenic cooling fluidic medium spray duration, and intervals between sprays, can be in the tens of milliseconds ranges, which allows surface cooling while still delivering the desired thermal effect into the deeper target tissue.
In various embodiments, the target tissue zone for therapy, also called therapeutic zone or thermal effect zone, can be at a tissue depth from approximately 100 ~m beneath the surface of the skin down to as deep as 10 millimeters, depending upon the type of treatment.
For treatments involving collagen contraction, it can be desirable to cool both the epidermis and the superficial layers of the dermis of the skin that lies beneath the epidermis, to a cooled depth range between 100 ~,m two millimeters. Different treatment algorithms can incorporate different amounts of pre-cooling, heating and post cooling phases in order to produce a desired tissue effect at a desired depth.
Various duty cycles, on and off times, of cooling and heating are utilized depending on the type of treatment. The cooling and heating duty cycles can be controlled and dynamically varied by an electronic control system known in the art.
Specifically the control system can be used to control cooling fluidic medium valve member 16 and the I~F power source.
The foregoing description of a prefeiTed embodiment of the invention has been presented for purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise forms disclosed. Obviously, many modifications and variations will be apparent to practitioners skilled in this art. It is intended that the scope of the invention be defined by the following claims and their equivalents.
In another embodiment of the present invention, an RF device includes a support structure. An RF electrode, coupled to the support structure, includes conductive and dielectric portions. At least portions of the RF electrode have different conductivities.
In another embodiment of the present invention, an RF device includes an RF
electrode with conductive and dielectric portions. A support structure is coupled to the RF
electrode. The support structure and the RF electrode form a seal where the support structure is coupled to the RF electrode.
In another embodiment of the present invention, an RF device includes an RF
electrode with conductive and dielectric portions. A support structure is coupled to the RF
electrode. A cooling member, coupled to the support structure, is configured to deliver cool a back surface of the RF electrode. The cooling member is distanced from the back surface of the RF electrode. The support structure and the RF electrode form a seal where the support structure is coupled to the I~F electrode.
EI~IEF I~ESCI~IPTI~~T ~F THE DI~AWII~CaS
Figure 1(a) is a cross-sectional view of one embodiment of the handpiece of the present invention.
Figure 1 (b) is a cross-sectional view of another embodiment of the RF device with a thermoelectric cooler.
Figure 2 is an exploded view of the Figure 1 RF electrode assembly.
Figure 3(a) is a close-up view of one embodiment of an RF electrode of the present invention.
Figure 3(b) illustrates one embodiment of an RF electrode, that can be utilized with the present invention, with an outer edge geometry configured to reduce an amount of capacitively coupled area the outer edge.
Figure 3(c) illustrates an one embodiment of an RF electrode, that can be utilized with the present invention, that has voids where there is little if any conductive material.
Figure 4 is a cross-sectional view of the RF electrode assembly from Figure 1.
Figure 5 is a side view of one embodiment of an RF handpiece assembly of the present invention.
Figure 6 is a rear view of the Figure 5 RF electrode assembly.
DETAILED DESCRIPTION
In various embodiments, the present invention provides methods for treating a tissue site. In one embodiment, an energy delivery surface of an energy delivery device is coupled to a skin surface. The coupling can be a direct, in contact, placement of the energy delivery surface of the energy delivery on the skin surface, or distanced relationship between the two with our without a media to conduct energy to the skin surface from the energy delivery surface of the energy delivery device. The skin surface is cooled sufficiently to create a reverse thermal gradient where a temperature of the skin surface is less than an underlying tissue. Energy is delivered from the energy delivery device to the underlying tissue area, resulting in a tissue effect at the skin surface.
Referring now to Figure 1 (a), the methods of present invention can be achieved with the use of a handpiece 10. Handpiece 10 is coupled with a handpiece assembly 12 that includes a handpiece housing 14 and a cooling fluitlic medium valve member 16.
Handpiece housing 14 is configured to be coupled to an electrode assembly 18. Electrode assembly 18 has a least one RF electrode 20 that is capacitively coupled to a skin surface when at least a portion of RF electrode 20 is in contact with the skin surface. Without limiting the scope of the present invention, RF electrode 20 can have a thickness in the range of 0.010 to 1.0 mm.
Handpiece 10 provides a more uniform thermal effect in tissue at a selected depth, while preventing or minimizing thermal damage to the skin surface and other non-target tissue. Handpiece 10 is coupled to an RF generator. RF electrode 20 can be operated either in mono-polar or bi-polar modes. Handpiece 10 is configured to reduce, or preferably eliminate edge effects and hot spots. The result is an improved aesthetic result/clinical outcome with an elimination/reduction in adverse effects and healing time.
A fluid delivery member 22 is coupled to cooling fluitlic medium valve member 16.
Fluid delivery member 22 and cooling fluitlic medium valve member 16 collectively form a cooling fluitlic medium dispensing assembly. Fluid delivery member 22 is configured to provide an atomizing delivery of a cooling fluitlic medium to RF electrode 20.
The atomizing delivery is a mist or fine spray. A phase transition, from liquid to gas, of the cooling fluitlic medium occurs when it hits the surface of RF electrode 20.
The transition from liquid to gas creates the cooling. If the transition before the cooling fluitlic medium hits RF electrode 20 the cooling of RF electrode 20 will not be as effective.
In another embodiment, illustrated in Figure 1(b), a thermo-electric cooler 23 is utilized in place of cooling fluitlic medium valve member 16 and fluid delivery member 22.
In one embodiment, the cooling fluitlic medium is a cryogenic spray, commercially available from Honeywell, Morristown, New Jersey. A specific example of a suitable cryogenic spray is R134A2, available from Refron, Inc., 38-18 33rd St" Long Island City, New York 11101. The use of a cryogenic cooling fluitlic medium provides the capability to use a number of different types of algorithms for skin treatment. For example, the cryogenic cooling fluitlic medium can be applied milliseconds before and after the delivery of RF
energy to the desired tissue. This is achieved with the use of cooling fluitlic medium valve member 16 coupled to a cryogen supply, including but not limited to a compressed gas canister. In various embodiments, cooling fluitlic medium valve member 16 can be coupled to a computer control system and/or manually controlled by the physician by means of a foot switch or similar device.
Providing a spray, or atomization, of cryogenic cooling fluitlic medium is particularly suitable because of it provides an availability to implement rapid on and off control.
Cryogenic cooling fluitlic medium allows more precise temporal control of the cooling process. This is because cooling only occurs when the refrigerant is sprayed and is in an evaporative state, the latter being a very fast short-lived event. Thus, cooling ceases rapidly after the cryogenic cooling fluitlic medium is stopped. The overall effect is to confer very precise time on-off control of cryogenic cooling fluitlic medium.
Referring now to Figure 2, fluid delivery member 22 and thenno-electric cooler can be positioned in handpiece housing 14 or electrode assembly 18. Fluid delivery member 22 is configured to controllably deliver a cooling fluitlic medium. Fluid delivery member 22 and thermo-electric cooler 23 cool a back surface 24 of RF electrode 20 and maintain back surface 24 at a desired temperature. The cooling fluitlic medium evaporatively cools RF
electrode 20 and maintains a substantially uniform temperature of front surface 26 of RF
electrode 20. Fluid delivery member 22 evaporatively cools baclc surface 24.
Front surface 26 may or may not be flexible and conformable to the skin, but it will still have sufficient strength and/or structure to provide good thermal coupling when pressed against the skin surface.
RF electrode 20 then conductively cools a skin surface that is adj acent to a front surface 26 of RF electrode 20. Suitable fluidic media include a variety of refrigerants such as R134A and freon.
Fluid delivery member 22 is configured to controllably deliver the cooling fluidic medium to back surface 24 at substantially any orientation of front surface 26 relative to a direction of gravity. A geometry and positioning of fluid delivery member 22 is selected to provide a substantially uniform distribution of cooling fluidic medium on back surface 24.
The delivery of the cooling fluidic medium can be by spray of droplets or fine mist, flooding back surface 24, and the like. Cooling occurs at the interface of the cooling fluidic medium with atmosphere, which is where evaporation occurs. If there is a thick layer of fluid on back surface 24 the heat removed from the treated skin will need to pass through the thick layer of cooling fluidic medium, increasing thermal resistance. To maximize cooling rates, it is desirable to apply a very thin layer of cooling fluidic medium. If RF
electrode 20 is not horizontal, and if there is a thick layer of cooling fluitlic medium, or if there are large drops of cooling fluitlic medium on back surface 24 , the cooling fluitlic medium can run down the surface of RF electrode 20 and pool at one edge or corner, causing uneven cooling.
Therefore, it is desirable to apply a thin layer of cooling fluitlic medium with a fine spray.
Thernio-electric cooler 23 achieves these same results but without delivering a cooling medium. Thermo-electric cooler 23 is cold on the side that is adjacent to or in contact with surface 24, while its opposing side becomes wanner.
In various embodiments, RF electrode 20, as illustrated in Figure 3(a), has a conductive portion 28 and a dielectric portion 30. Conductive portion 28 can be a metal including but not limited to copper, gold, silver, aluminum and the like.
Dielectric portion 30 can be made of a variety of different materials including but not limited to polyimide, Teflon~ and the lilce, silicon nitride, polysilanes, polysilazanes, polyimides, I~apton and other polymers, antenna dielectrics and other dielectric materials well known in the art. Other dielectric materials include but are not limited to polymers such as polyester, silicon, sapphire, diamond, zirconium-toughened alumina (ZTA), alumina and the like.
Dielectric portion 30 can be positioned around at least a portion, or the entirety of a periphery of conductive portion 28. In another embodiment, RF electrode 20 is made of a composite material, including but not limited to gold-plated copper, copper-polyimide, silicon/silicon-nitride and the like.
Dielectric portion 30 creates an increased impedance to the flow of electrical current through RF electrode 20. This increased impedance causes current to travel a path straight down through conductive portion 28 to the skin surface. Electric field edge effects, caused by a concentration of current flowing out of the edges of RF electrode 20, are reduced.
Dielectric portion 30 produces a more uniform impedance through RF electrode and causes a more uniform current to flow through conductive portion 28. The resulting effect minimizes or even eliminates, edge effects around the edges of RF
electrode 20. As shown in Figure 3(c), RF electrode 20 can have voids 33 where there is little or no conductive material. Creating voids 33 in the conductive material alters the electric field. The specific configuration of voids can be used to minimize edge effect, or alter the depth, uniformity or shape of the electric field. Under a portion 28'of the RF electrode 20 with solid conductive material the electric field is deeper. Under a portion 28"of RF electrode 20 with more voids, the electric field is shallower. By combining different densities of conductive material, an RF
electrode 20 is provided to match the desired heating profile.
In one embodiment, conductive portion 28 adheres to dielectric portion 30 which can be a substrate with a thickness, by way of example and without limitation, of about 0.001".
This embodiment is similar to a standard flex circuit board material commercially available in the electronics industry. In this embodiment, dielectric pot-tion 30 is in contact with the tissue, the skin, and conductive portion 28 is separated from the skin.
The thickness of the dielectric portion 30 can be decreased by growing conductive portion 28 on dielectric portion 30 using a variety of techniques, including but not limited to, sputtering, electro deposition, chemical vapor deposition, plasma deposition and other deposition teclmiques known in the art. Additionally, these same processes can be used to deposit dielectric portion 30 onto conductive portion 28. In one embodiment dielectric portion 30 is an oxide layer which can be grown on conductive portion 28. An oxide layer has a low thernlal resistance and improves the cooling efficiency of the skin compared with many other dielectrics such as polymers.
In various embodiments, RF electrode 20 is configured to inhibit the capacitive coupling to tissue along its outside edge 31. Referring to Figure 3(b) RF
electrode 20 can have an outer edge 31 with a geometry that is configured to reduce an amount of capacitively coupled area at outer edge 31. Outer edge 31 can have less of the conductive portion 28 material. This can be achieved by different geometries, including but not limited to a scalloped geometry, and the like. The total length of outer edge 31 can be increased, with different geometries, and the total area that is capacitively coupled to tissue is reduced. This produces a reduction in energy generation around outer edge 31.
Alternatively, the dielectric material can be applied in a thicker layer at the edges, reducing the electric field at the edges. A further alternative is to configure the cooling to cool more aggressively at the edges to compensate for any electric field edge effect.
Fluid delivery member 22 has an inlet 32 and an outlet 34. Outlet 34 can have a smaller cross-sectional area than a cross-sectional area of inlet 32. In one embodiment, fluid delivery member 22 is a nozzle 36.
Cooling fluidic medium valve member 16 can be configured to provide a pulsed delivery of the cooling fluidic medium. Pulsing the delivery of cooling fluidic medium is a simple way to control the rate of cooling fluidic medium application. In one embodiment, cooling fluidic medium valve member 16 is a solenoid valve. An example of a suitable solenoid valve is a solenoid pinch valve manufactured by the N-Research Corporation, West Caldwell, NJ. If the fluid is pressurized, then opening of the valve results in fluid flow. If the fluid is maintained at a constant pressure, then the flow rate is constant and a simple open/close solenoid valve can be used, the effective flow rate being determined by the pulse duty cycle. A higher duty cycle, close to 100°/~ increases cooling, while a lower duty cycle, closer to 0%, reduces cooling. The duty cycle can be achieved by turning on the valve for a short duration of time at a set frequency. The duration of the open time can be 1 to 50 milliseconds or longer. The frequency of pulsing can be 1 to 50 I-Iz or faster.
Alternatively, cooling fluidic medium flow rate can be controlled by a metering valve or controllable-rate pump such as a peristaltic pump. One advantage of pulsing is that it is easy to control using simple electronics and control algorithms.
Electrode assembly 18 is sufficiently sealed so that the cooling fluidic medium does not leak from back surface 24 onto a skin surface in contact with a front surface of RF
electrode 20. This helps provide an even energy delivery through the skin surface. In one embodiment, electrode assembly 18, and more specifically RF electrode 20, has a geometry that creates a reservoir at back surface 24 to hold and gather cooling fluidic medium that has collected at back surface 24. Back surface 24 can be formed with "hospital corners" to create this reservoir. Optionally, electrode assembly 18 includes a vent that permits vaporized cooling fluidic medium to escape from electrode assembly 18.
The vent prevents pressure from building up in electrode assembly 18. The vent can be a pressure relief valve that is vented to the atmosphere or a vent line.
When the cooling fluidic medium comes into contact with RF electrode 20 and evaporates, the resulting gas pressurizes the inside of electrode assembly 18. This can cause RF electrode 20 to partially inflate and bow out from front surface 26. The inflated RF electrode 20 can enhance the thermal contact with the skin and also result in some degree of conformance of RF electrode 20 to the skin surface. An electronic controller can be provided. The electronic controller sends a signal to open the vent when a programmed pressure has been reached.
Various leads 40 are coupled to RF electrode 20. One or more thermal sensors 42 are coupled to RF electrode. Suitable thermal sensors 42 include but are not limited to thermocouples, thermistors, infrared photo-emitters and a thermally sensitive diode. In one embodiment, a thermal sensor 42 is positioned at each corner of RF electrode 20. A sufficient number of thermal sensors 42 are provided in order to acquire sufficient thermal data of the skin surface or the back surface 24 of the electrode 20. Thermal sensors 42 are electrically isolated from RF electrode 20. In another embodiment, at least one sensor 42 is positioned at baclc surface 24 of RF electrode and detects the temperature of back surface 24 in response to the delivery of cooling fluidic medium.
Thermal sensors 4.2 measure temperature and can provide feedback for monitoring temperature of RF electrode 20 and/or the tissue during treatment.. Thermal sensors 42 can be thermistors, thermocouples, thermally sensitive diodes, capacitors, inductors or other devices for measuring temperature. Preferably, thermal sensors 4.2 provide electronic feedback to a microprocessor of the RF generator coupled to RF°
electrode 20 in order to facilitate control of the treatment.
Measurements from thermal sensors 42 can be used to help control the rate of application of cooling fluitlic medium. For example, a cooling control algoritlun can be used to apply cooling fluitlic medium to RF electrode 20 at a high flow rate until the temperature fell below a target temperature, and then slow down or stop. A PID, or proportional-integral-differential, algorithm can be used to precisely control RF electrode 20 temperature to a predetermined value.
Thermal sensors 42 can be positioned on back surface 24 of RF electrode 20 away from the tissue. This configuration is preferable for controlling the temperature of the RF
electrode 20. Alternatively, thermal sensors 42 can be positioned on front surface 26 of RF
electrode 10 in direct contact with the tissue. This embodiment can be more suitable for monitoring tissue temperature. Algorithms are utilized with thermal sensors 42 to calculate a temperature profile of the treated tissue. Thermal sensors 42 can be used to develop a temperature profile of the skin which is then used for process control purposes to assure that the proper amounts of heating and cooling are delivered to achieve a desired elevated deep , tissue temperature while maintaining skin tissue layers below a threshold temperature and avoid thermal injury.
The physician can use the measured temperature profile to assure that he stays within the boundary of an ideal/average profile for a given type of treatment.
Thermal sensors 42 can be used for additional purposes. When the temperature of thermal sensors 42 is monitored it is possible to detect when RF electrode 20 is in contact with the skin surface.
This can be achieved by detecting a direct change in temperature when skin contact is made or examining the rate of change of temperature which is affected by contact with the skin.
Similarly, if there is more than one thermal sensor 42, the thermal sensors 42 can be used to detect whether a portion of RF electrode 20 is lifted or out of contact with skin. This can be important because the current density (amperes per unit area) delivered to the skin can vary if the contact area changes. In particular, if part of the surface of RF
electrode 20 is not in contact with the skin, the resulting current density is higher than expected.
Deferring again to Figure 1(a), a force sensor 44 is also coupled to electrode assembly 1 ~. Force sensor 44~ detects an amount of force applied by electrode assembly 1 S, via the physician, against an applied skin surface. Force sensor 44 zeros out gravity effects of the weight of electrode assembly 1 ~ in any orientation of front surface 26 of RF
electrode 20 relative to a direction of gravity. Additionally, force sensor 44 provides an indication when DF electrode 20 is in contact with a skin surface. Force sensor 44 also provides a signal indicating that a force applied by DF electrode 20 to a contacted skin surface is, (i) above a minimum threshold or (ii) below a maximum threshold.
As illustrated in Figure 4, an activation button 46 is used in conjunction with the force sensor. Just prior to activating DF electrode 20, the physician holds handpiece 10 in position just off the surface of the slcin. The orientation of handpiece 10 can be any angle relative to the direction of gravity. To arm handpiece 10, the physician can press activation button 46 which tares force sensor 44, by setting it to read zero. This cancels the force due to gravity in that particular treatment orientation. This method allows consistent force application of RF
electrode 20 to the skin surface regardless of the angle of handpiece 10 relative to the direction of gravity.
RF electrode 20 can be a flex circuit, which can include trace components.
Additionally, thermal sensor 42 and force sensor 44 can be part of the flex circuit. Further, the flex circuit can include a dielectric that forms a part of RF electrode 20.
Electrode assembly 18 can be moveably positioned within handpiece housing 12.
In one embodiment, electrode assembly 18 is slideably moveable along a longitudinal axis of handpiece housing 12.
Electrode assembly 18 can be rotatably mounted in handpiece housing 12.
Additionally, RF electrode 20 can be rotatably positioned in electrode assembly 18.
Electrode assembly 18 can be removably coupled to handpiece housing 12 as a disposable or non-disposable RF device 52.
For purposes of this disclosure, electrode assembly 18 is the same as RF
device 52.
Qnce movably mounted to handpiece housing 12, RF device 52 can be coupled to handpiece housing 12 via force sensor 44. Force sensor 44 can be of the type that is capable of measuring both compressive and tensile forces. In other embodiments, force sensor 44 only measures compressive forces, or only measures tensile forces.
RF device 52 can be spring-loaded with a spring 48. In one embodiment, spring biases RF electrode 20 in a direction toward handpiece housing 12. This pre-loads force sensor 44 and keeps RF device 52 pressed against force sensor 44.. The pre-load force is tared when activation button 46 is pressed just prior to application of RF
electrode 20 to the skin surface.
A shroud 50 is optionally coupled to handpiece 10. Shroud 50 serves to keep the user from touching RF device 52 during use which can cause erroneous force readings.
A non-volatile memory 54 can be included with RF device 52. Additionally, non-volatile memory can be included with handpiece housing 12. Non-volatile memory 54 can be an EPR~M and the like. Additionally, a second non-volatile memory can be included in handpiece housing 12 for purposes of storing handpiece 10 information such as but not limited to, handpiece model number or version, handpiece software version, number of RF
applications that handpiece 10 has delivered, expiration date and manufacture date.
Handpiece housing 12 can also contain a microprocessor 58 for purposes of acquiring and analyzing data from various sensors on handpiece housing 12 or RF device 52 including but not limited to thermal sensors 42 , force sensors 44, fluid pressure gauges, switches, buttons and the like.
Microprocessor 58 can also control components on handpiece 10 including but not limited to lights, LEDs, valves, pumps or other electronic components.
Microprocessor 58 can also communicate data to a microprocessor of the RF generator.
Non-volatile memory 54 can store a variety of data that can facilitate control and operation of handpiece 10 and its associated system including but not limited to, (i) controlling the amount of current delivered by RF electrode 20, (ii) controlling the duty cycle of the fluid delivery member 22 and thermo-electric cooler 23, (iii) controlling the energy delivery duration time of the RF electrode 20, (iv) controlling the temperature of RF electrode 20 relative to a target temperature, (v) providing a maximum number of firings of RF
electrode 20, (vi) providing a maximum allowed voltage that is deliverable by RF electrode 20, (vii) providing a history of RF electrode 20 use, (viii) providing a controllable duty cycle to fluid delivery member 22 and thermo-electric cooler 23 for the delivery of the cooling fluidic medium to back surface 24 of RF electrode 20, (ix) providing a controllable delivery rate of cooling fluidic medium delivered from fluid delivery member 22 to back surface 24, (x) providing a control of thermo-electric cooler 23 and the like.
F~eferring now to Figures 5 and 6, FtF device 52 includes a support structure, including but not limited to a housing 60 that defines the body of I~F device 52. 1tF
device 52 can include a baclc plate 62 that is positioned at a proximal portion of support structure 60. A
plurality of electrical contact pads 64 can be positioned at back plate 62. At least a portion of fluid delivery member 22 and thermo-electric cooler 23 can extend through back plate 62.
Fluid delivery nlenlber 22 can be a channel with a proximal end that is raised above the back surface of back plate 62.
First and second engagement members 64 can also be formed in the body of support structure 60. Engagement members 64 provide engagement and disengagement with handpiece housing 14. Suitable engagement members 64 include but are not limited to snap members, apertures to engage with snap members of substrate support 60, and the like.
Handpiece 10 can be used to deliver thermal energy to modify tissue including, but not limited to, collagen containing tissue, in the epidermal, dermal and subcutaneous tissue layers, including adipose tissue. The modification of the tissue includes modifying a physical feature of the tissue, a structure of the tissue or a physical property of the tissue. The modification can be achieved by delivering sufficient energy to modify collagen containing tissue, cause collagen shrinkage, and/or a wound healing response including the deposition of new or nascent collagen, and the like.
Handpiece 10 can be utilized for performing a number of treatments of the skin and underlying tissue including but not limited to, (i) dermal remodeling and tightening, (ii) wrinkle reduction, (iii) elastosis reduction, (iv) scar reduction, (v) sebaceous gland removal/deactivation and reduction of activity of sebaceous gland, (vi) hair follicle removal, (vii) adipose tissue remodeling/removal, (viii) spider vein removal, (ix) modify contour irregularities of a skin surface, (x) create scar or nascent collagen, (xi) reduction of bacteria activity of skin, (xii) reduction of skin pore size, (xiii) unclog skin pores and the like.
In various embodiments, handpiece 10 can be utilized in a variety of treatment processes, including but not limited to, (i) pre-cooling, before the delivery of energy to the tissue has begun, (ii) an on phase or energy delivery phase in conjunction with cooling and (iii) post cooling after the delivery of energy to tissue has stopped.
Handpiece 10 can be used to pre-cool the surface layers of the target tissue so that when RF electrode 20 is in contact with the tissue, or prior to turning on the RF energy source, the superficial layers of the target tissue are already cooled. When RF energy source is turned on or delivery of RF to the tissue otherwise begins, resulting in heating of the tissues, the tissue that has been cooled is protected from thermal effects including thermal damage. The tissue that has not been cooled will warm up to therapeutic temperatures resulting in the desired therapeutic effect.
Pre-cooling gives time for the thermal effects of cooling to propagate down into the tissue. More specifically, pre-cooling allows the achievement of a desired tissue depth thermal profile, with a minimum desired temperature being achieved at a selectable depth.
The amount or duration of pre-cooling can be used to select the depth of the protected zone of untreated tissue. Longer durations of pre-cooling produce a deeper protected zone and hence a deeper level in tissue for the start of the treatment zone. The opposite is true for shorter periods of pre-cooling. The temperature of front surface 26 of hF electrode 20 also affects the temperature profile. The colder the temperature of front surface 26, the faster and deeper the cooling, and vice verse.
Post-cooling can be important because it prevents and/or reduces heat delivered to the deeper layers from conducting upward and heating the more superficial layers possibly to therapeutic or damaging temperature range even though external energy delivery to the tissue has ceased. In order to prevent this and related thermal phenomena, it can be desirable to maintain cooling of the treatment surface for a period of time after application of the RF
energy has ceased. In various embodiments, varying amounts of post cooling can be combined with real-time cooling and/or pre-cooling.
In various embodiments, handpiece 10 can be used in a varied number of pulse on-off type cooling sequences and algorithms may be employed. In one embodiment, the treatment algorithm provides for pre-cooling of the tissue by starting a spray of cryogenic cooling fluidic medium, followed by a short pulse of RF energy into the tissue. In this embodiment, the spray of cryogenic cooling fluidic medium continues while the RF energy is delivered, and is stopping shortly thereafter, e.g. on the order of milliseconds. This or another treatment sequence can be repeated again. Thus in various embodiments, the treatment sequence can include a pulsed sequence of cooling on, heat, cooling off, cooling on, heat, cool off, and with cooling and heating durations on orders of tens of milliseconds. In these embodiments, every time the surface of the tissue of the skin is cooled, heat is removed from the skin surface.
Cryogenic cooling fluidic medium spray duration, and intervals between sprays, can be in the tens of milliseconds ranges, which allows surface cooling while still delivering the desired thermal effect into the deeper target tissue.
In various embodiments, the target tissue zone for therapy, also called therapeutic zone or thermal effect zone, can be at a tissue depth from approximately 100 ~m beneath the surface of the skin down to as deep as 10 millimeters, depending upon the type of treatment.
For treatments involving collagen contraction, it can be desirable to cool both the epidermis and the superficial layers of the dermis of the skin that lies beneath the epidermis, to a cooled depth range between 100 ~,m two millimeters. Different treatment algorithms can incorporate different amounts of pre-cooling, heating and post cooling phases in order to produce a desired tissue effect at a desired depth.
Various duty cycles, on and off times, of cooling and heating are utilized depending on the type of treatment. The cooling and heating duty cycles can be controlled and dynamically varied by an electronic control system known in the art.
Specifically the control system can be used to control cooling fluidic medium valve member 16 and the I~F power source.
The foregoing description of a prefeiTed embodiment of the invention has been presented for purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise forms disclosed. Obviously, many modifications and variations will be apparent to practitioners skilled in this art. It is intended that the scope of the invention be defined by the following claims and their equivalents.
Claims (157)
1. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions; and a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions; and a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode.
2. The RF device of claim 1, wherein the cooling member includes a valve.
3. The RF device of claim 1, wherein the cooling member includes a nozzle.
4. The RF device of claim 1, wherein the cooling member is configured to deliver a controllable amount of cooling fluidic medium to the RF electrode.
5. The RF device of claim 1, wherein the cooling member is configured to deliver a cooling fluidic medium to the back of the RF electrode to evaporatively cool the RF
electrode and conductively cool a skin surface in contact with a skin interface surface of the RF electrode.
electrode and conductively cool a skin surface in contact with a skin interface surface of the RF electrode.
6. The RF device of claim 1, wherein the cooling member is a thermo-electric cooler.
7. The RF device of claim 1, further comprising:
a back plate positioned at a proximal portion of the support structure.
a back plate positioned at a proximal portion of the support structure.
8. The RF device of claim 7, further comprising:
a plurality of electrical contact pads coupled to the back plate.
a plurality of electrical contact pads coupled to the back plate.
9. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, and a flex circuit;
a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, and a flex circuit;
a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode.
10. The RF device of claim 9, wherein the cooling member includes a valve.
11. The RF device of claim 9, wherein the cooling member includes a nozzle
12. The RF device of claim 9, wherein the cooling member is configured to deliver a controllable amount of cooling fluidic medium to the RF electrode.
13. The RF device of claim 9, wherein the cooling member is configured to deliver a deliver a cooling fluidic medium to the back of the RF electrode to evaporatively cool the RF electrode and conductively cool a skin surface in contact with a skin interface surface of the RF electrode.
14. The RF device of claim 9, wherein the cooling member is a thermo-electric cooler.
15. The RF device of claim 9, further comprising:
a back plate positioned at a proximal portion of the support structure.
a back plate positioned at a proximal portion of the support structure.
16. The RF device of claim 15, further comprising:
a plurality of electrical contact pads coupled to the back plate.
a plurality of electrical contact pads coupled to the back plate.
17. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and having conductive and dielectric portions; and first and second engagement members formed in the body of the support structure, the first and second engagement members providing engagement and disengagement with a handpiece support structure.
a support structure;
an RF electrode coupled to the support structure and having conductive and dielectric portions; and first and second engagement members formed in the body of the support structure, the first and second engagement members providing engagement and disengagement with a handpiece support structure.
18. The RF device of claim 17, wherein each of the first and second engagement members is snap member.
19. The RF device of claim 17, wherein each of the first and second engagement members include an aperture configured to receive a snap member of a handpiece support structure.
20. The RF device of claim 17, wherein the RF electrode has a tissue interface surface and an opposing back surface.
21. The RF device of claim 20, further comprising:
a back plate positioned at a distal portion of the support structure, the back plate including a back surface and an opposing front surface that faces the back surface of the RF
electrode.
a back plate positioned at a distal portion of the support structure, the back plate including a back surface and an opposing front surface that faces the back surface of the RF
electrode.
22. The RF device of claim 20, further comprising:
a cooling member configured to cool the back surface of the RF electrode.
a cooling member configured to cool the back surface of the RF electrode.
23. The RF device of claim 22, wherein at least a portion of the cooling member extends through the back plate.
24. The RF device of claim 23, wherein the cooling member has a proximal end that is raised above the back surface of the back plate.
25. The RF device of claim 17, wherein the RF electrode is configured to be capacitively coupled when at least a portion of the RF electrode is in contact with a skin surface.
26. The RF device of claim 17, further comprising:
a flex circuit coupled to the RF electrode.
a flex circuit coupled to the RF electrode.
27. An RF device, comprising:
a support structure;
an RF electrode including conductive and dielectric portions, the RF electrode configured to be capacitively coupled when at least a portion of the RF
electrode is in contact with a skin surface;
a back plate positioned at a proximal portion of the support structure; and a plurality of electrical contact pads coupled to the baclc plate.
a support structure;
an RF electrode including conductive and dielectric portions, the RF electrode configured to be capacitively coupled when at least a portion of the RF
electrode is in contact with a skin surface;
a back plate positioned at a proximal portion of the support structure; and a plurality of electrical contact pads coupled to the baclc plate.
28. The RF device of claim 27, wherein the support structure includes first and second engagement members that provide engagement and disengagement with a handpiece support structure.
29. The RF device of claim 27, wherein the RF electrode has a tissue interface surface and an opposing back surface.
30. The RF device of claim 29, wherein the back plate includes a back surface and an opposing front surface that faces the back surface of the RF electrode.
31. The RF device of claim 30, further comprising:
a cooling member configured to cool the back surface of the RF electrode.
a cooling member configured to cool the back surface of the RF electrode.
32. The RF device of claim 31, wherein at least a portion of the cooling member extends through the back plate.
33. The RF device of claim 32, wherein the cooling member has a proximal end that is raised above the back surface of the back plate.
34. The RF device of claim 31, wherein the cooling member is a thermo-electric cooler.
35. The RF device of claim 27, further comprising:
a flex circuit coupled to the RF electrode.
a flex circuit coupled to the RF electrode.
36. An RF device, comprising:
a support structure;
an RF electrode including conductive and dielectric portions, a tissue interface surface and an opposing back surface, a back plate positioned at a proximal portion of the support structure, the back plate including a front surface that faces the opposing back surface of the RF
electrode and an opposing back surface; and a cooling member with a channel with a distal section that extends through the back plate and a proximal section that is raised above the back surface of the back plate.
a support structure;
an RF electrode including conductive and dielectric portions, a tissue interface surface and an opposing back surface, a back plate positioned at a proximal portion of the support structure, the back plate including a front surface that faces the opposing back surface of the RF
electrode and an opposing back surface; and a cooling member with a channel with a distal section that extends through the back plate and a proximal section that is raised above the back surface of the back plate.
37. The RF device of claim 36, wherein the RF electrode includes conductive and dielectric portions, wherein the RF electrode is configured to be capacitively coupled when at least a portion of the RF electrode is in contact with a skin surface;
38. The RF device of claim 36, wherein the support structure includes first and second engagement members that provide engagement and disengagement with a handpiece support structure.
39. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and at least a first sensor coupled to the RF electrode.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and at least a first sensor coupled to the RF electrode.
40. The RF device of claim 39, further comprising:
a second sensor coupled to the RF electrode.
a second sensor coupled to the RF electrode.
41. The RF device of claim 39, wherein the at least first sensor is positioned at the tissue interface surface.
42. The 12F device of claim 39, further comprising:
a non-volatile memory coupled to the RF electrode.
a non-volatile memory coupled to the RF electrode.
43. The RF device of claim 39, wherein the cooling member is configured to deliver a cooling fluidic medium to a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode.
44. The RF device of claim 39, wherein the cooling member is a thermo-electric cooler.
45. RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and a non-volatile memory coupled to the support structure.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and a non-volatile memory coupled to the support structure.
46. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and having conductive and dielectric portions; and a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode.
a support structure;
an RF electrode coupled to the support structure and having conductive and dielectric portions; and a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode.
47. The RF device of claim 46, wherein the cooling member includes a valve.
48. The RF device of claim 46, wherein the cooling member includes a nozzle.
49. The RF device of claim 46, wherein the cooling member is configured to deliver a controllable amount of cooling fluidic medium to the RF electrode.
50. The RF device of claim 46, wherein the cooling member is configured to deliver a cooling fluidic medium to the back of the RF electrode to evaporatively cool the RF
electrode and conductively cool a skin surface in contact with a skin interface surface of the RF electrode.
electrode and conductively cool a skin surface in contact with a skin interface surface of the RF electrode.
51. The RF device of claim 46, further comprising:
a back plate positioned at a proximal portion of the support structure.
a back plate positioned at a proximal portion of the support structure.
52. The RF device of claim 51, further comprising:
a plurality of electrical contact pads coupled to the back plate.
a plurality of electrical contact pads coupled to the back plate.
53. An RF device, comprising:
a support structure defining a body of an RF device;
an RF electrode with conductive and dielectric portions, the RF electrode including a flex circuit;
a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode.
a support structure defining a body of an RF device;
an RF electrode with conductive and dielectric portions, the RF electrode including a flex circuit;
a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode.
54. The RF device of claim 53, wherein the cooling member includes a valve.
55. The RF device of claim 53, wherein the cooling member includes a nozzle
56. The RF device of claim 53, wherein the cooling member is configured to deliver a controllable amount of cooling fluidic medium to the RF electrode.
57. The RF device of claim 53, wherein the cooling member is configured to deliver a deliver a cooling fluidic medium to the back of the RF electrode to evaporatively cool the RF electrode and conductively cool a skin surface in contact with a skin interface surface of the RF electrode.
58. The RF device of claim 53, wherein the cooling member is a thermo-electric cooler.
59. The RF device of claim 53, further comprising:
a back plate positioned at a proximal portion of the support structure.
a back plate positioned at a proximal portion of the support structure.
60. The RF device of claim 59, further comprising:
a plurality of electrical contact pads coupled to the back plate.
a plurality of electrical contact pads coupled to the back plate.
61. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions; and first and second engagement members formed in the body of the support structure, the first and second engagement members providing engagement and disengagement with a handpiece support structure.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions; and first and second engagement members formed in the body of the support structure, the first and second engagement members providing engagement and disengagement with a handpiece support structure.
62. The RF device of claim 61, wherein each of the first and second engagement members is snap member.
63. The RF device of claim 61, wherein each of the first and second engagement members includes an aperture configured to receive a snap member of a handpiece support structure.
64. The RF device of claim 61, wherein the RF electrode has a tissue interface surface and an opposing back surface.
65. The RF device of claim 64, further comprising:
a back plate positioned at a distal portion of the support structure, the back plate including a back surface and an opposing front surface that faces the back surface of the RF
electrode.
a back plate positioned at a distal portion of the support structure, the back plate including a back surface and an opposing front surface that faces the back surface of the RF
electrode.
66. The RF device of claim 64, further comprising:
a cooling member configured to cool the back surface of the RF electrode.
a cooling member configured to cool the back surface of the RF electrode.
67. The RF device of claim 66, wherein at least a portion of the cooling member extends through the back plate.
68. The RF device of claim 67, wherein the cooling member has a proximal end that is raised above the back surface of the back plate.
69. The RF device of claim 66, wherein the cooling member is a thermo-electric cooler.
70. The RF device of claim 61, wherein the RF electrode is configured to be capacativly coupled when at least a portion of the RF electrode is in contact with a skin surface.
71. The RF device of claim 61, further comprising:
a flex circuit coupled to the 12F electrode.
a flex circuit coupled to the 12F electrode.
72. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode configured to be capacativly coupled when at least a portion of the RF electrode is in contact with a skin surface;
a back plate positioned at a proximal portion of the support structure; and a plurality of electrical contact pads coupled to the balls plate.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode configured to be capacativly coupled when at least a portion of the RF electrode is in contact with a skin surface;
a back plate positioned at a proximal portion of the support structure; and a plurality of electrical contact pads coupled to the balls plate.
73. The RF device of claim 72, wherein the support structure includes first and second engagement members that provide engagement and disengagement with a handpiece support structure.
74. The RF device of claim 72, wherein the RF electrode has a tissue interface surface and an opposing back surface.
75. The RF device of claim 74, wherein the back plate includes a back surface and an opposing front surface that faces the back surface of the RF electrode.
76. The RF device of claim 75, further comprising:
a cooling member configured to cool the back surface of the RF electrode.
a cooling member configured to cool the back surface of the RF electrode.
77. The RF device of claim 76, wherein at least a portion of the cooling member extends through the back plate.
78. The RF device of claim 77, wherein the cooling member has a proximal end that is raised above the back surface of the back plate.
79. The RF device of claim 76, wherein the cooling member is a thermo-electric cooler.
80. The RF device of claim 72, further comprising:
a flex circuit coupled to the RF electrode.
a flex circuit coupled to the RF electrode.
81. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, a tissue interface surface and an opposing back surface, a back plate positioned at a proximal portion of the support structure, the back plate including a front surface that faces the opposing back surface of the RF
electrode and an opposing back surface; and a cooling member with a channel with a distal section that extends through the back plate and a proximal section that is raised above the back surface of the back plate.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, a tissue interface surface and an opposing back surface, a back plate positioned at a proximal portion of the support structure, the back plate including a front surface that faces the opposing back surface of the RF
electrode and an opposing back surface; and a cooling member with a channel with a distal section that extends through the back plate and a proximal section that is raised above the back surface of the back plate.
82. The RF device of claim 81, wherein the RF electrode includes conductive and dielectric portions, wherein the RF electrode is configured to be capacativly coupled when at least a portion of the RF electrode is in contact with a skin surface;
83. The RF device of claim 81, wherein the support structure includes first and second engagement members that provide engagement and disengagement with a handpiece support structure.
84. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and at least a first sensor coupled to the RF electrode.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and at least a first sensor coupled to the RF electrode.
85. The RF device of claim 84, further comprising:
a second sensor coupled to the RF electrode.
a second sensor coupled to the RF electrode.
86. The RF device of claim 84, wherein the at least first sensor is positioned at the back surface.
87. The RF device of claim 86, wherein the at least first sensor detects a temperature of the back surface.
88. The RF device of claim 85, further comprising:
a non-volatile memory coupled to the RF electrode.
a non-volatile memory coupled to the RF electrode.
89. The RF device of claim 84, wherein the cooling member is configured to deliver a cooling fluidic medium to a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode.
90. The RF device of claim 84, wherein the cooling member is a thermo-electric cooler.
91. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and a non-volatile memory coupled to the support structure.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface;
a cooling member coupled to the support structure; and a non-volatile memory coupled to the support structure.
92. An RF device, comprising:
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface and having and outer edge with a geometry configured to reduce an amount of capacitively coupled area at the outer edge.
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface and having and outer edge with a geometry configured to reduce an amount of capacitively coupled area at the outer edge.
93. The RF device of claim 92, wherein an interior of the RF electrode has a larger amount of capacitive coupling to a skin surface than the outer edge.
94. The RF device of claim 92, wherein the geometry is selected to reduce an amount of the conductive portion at the outer edge.
95. The RF device of claim 92, wherein the outer edge has a scalloped geometry to reduce an amount of conductive material at the outer edge.
96. The RF device of claim 92, further comprising:
a flee circuit coupled to the RF electrode.
a flee circuit coupled to the RF electrode.
97. The RF device of claim 92, further comprising:
a backplate coupled to the support structure; and a plurality of electrical contact pads coupled to the back plate.
a backplate coupled to the support structure; and a plurality of electrical contact pads coupled to the back plate.
98. The RF device of claim 92, wherein the support structure includes first and second engagement members that provide engagement and disengagement with a handpiece support structure.
99. The RF device of claim 92, further comprising:
at least a first sensor coupled to the RF electrode.
at least a first sensor coupled to the RF electrode.
100. The RF device of claim 99, wherein the at least first sensor is positioned at the back surface.
101. The RF device of claim 100, wherein the at least first sensor detects a temperature of the back surface.
102. The RF device of claim 92, further comprising:
a non-volatile memory coupled to the RF electrode.
a non-volatile memory coupled to the RF electrode.
103. An RF device, comprising:
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface, wherein at least a portion of the RF electrode has voids that reduce an amount of conductive material in the RF electrode.
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface, wherein at least a portion of the RF electrode has voids that reduce an amount of conductive material in the RF electrode.
104. The RF device of claim 103, further comprising:
a flex circuit coupled to the RF electrode.
a flex circuit coupled to the RF electrode.
105. The RF device of claim 103, further comprising:
a backplate coupled to the support structure; and a plurality of electrical contact pads coupled to the back plate.
a backplate coupled to the support structure; and a plurality of electrical contact pads coupled to the back plate.
106. The RF device of claim 103, wherein the support structure includes first and second engagement members that provide engagement and disengagement with a handpiece support structure.
107. The RF device of claim 103, further comprising:
at least a first sensor coupled to the RF electrode.
at least a first sensor coupled to the RF electrode.
108. The RF device of claim 107, wherein the at least first sensor is positioned at the back surface.
109. The RF device of claim 108, wherein the at least first sensor detects a temperature of the back surface.
110. The RF device of claim 103, further comprising:
a non-volatile memory coupled to the RF electrode.
a non-volatile memory coupled to the RF electrode.
111. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode being configured to provide a controllable tissue effect on subcutaneous tissue while preserving an epidermal skin surface overlying the subcutaneous tissue.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions, the RF electrode being configured to provide a controllable tissue effect on subcutaneous tissue while preserving an epidermal skin surface overlying the subcutaneous tissue.
112. The RF device of claim 111, wherein the subcutaneous tissue includes fat tissue.
113. The RF device of claim 111, wherein the subcutaneous tissue includes muscle tissue.
114. The RF device of claim 111, wherein the RF electrode includes an RF
tissue interface surface and an opposing back surface.
tissue interface surface and an opposing back surface.
115. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure; and a flex circuit coupled to the RF electrode.
a support structure;
an RF electrode coupled to the support structure; and a flex circuit coupled to the RF electrode.
116. An RF device, comprising:
a support structure;
an RF electrode;
a flex circuit coupled to the RF electrode; and a plurality of electrical contact pads coupled to the flex circuit.
a support structure;
an RF electrode;
a flex circuit coupled to the RF electrode; and a plurality of electrical contact pads coupled to the flex circuit.
117. An RF device, comprising:
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions; and a plurality of electrical contact pads coupled to the RF electrode.
a support structure;
an RF electrode coupled to the support structure and including conductive and dielectric portions; and a plurality of electrical contact pads coupled to the RF electrode.
118. An RF device, comprising:
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, at least portions of the RF electrode having different widths.
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, at least portions of the RF electrode having different widths.
119. An RF device, comprising:
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, at least.portions of the RF electrode having different conductivities.
a support structure; and an RF electrode coupled to the support structure and including conductive and dielectric portions, at least.portions of the RF electrode having different conductivities.
120. An RF device, comprising:
an RF electrode with conductive and dielectric portions; and a support structure coupled to the RF electrode, the support structure and the RF
electrode forming a seal where the support structure is coupled to the RF
electrode.
an RF electrode with conductive and dielectric portions; and a support structure coupled to the RF electrode, the support structure and the RF
electrode forming a seal where the support structure is coupled to the RF
electrode.
121. The RF device of claim 120, wherein the seal is a fluid tight seal.
122. The RF device of claim 120, wherein the RF electrode has a front surface and an opposing back surface.
123. The RF device of claim 122, wherein the back surface is positioned to be cooled and the front surface is positioned to deliver energy to a tissue surface.
124. The RF device of claim 122, wherein the back surface is positioned to be cooled by a fluid.
125. The RF device of claim 123, wherein the fluid is a gas.
126. The RF device of claim 123, wherein the fluid is a liquid.
127. The RF device of claim 123, further comprising:
a sensor coupled to the RF electrode.
a sensor coupled to the RF electrode.
128. The RF device of claim 127, wherein the sensor is positioned at the back surface of the RF electrode.
129. The RF device of claim 128, wherein the sensor detects a temperature of the back surface of the RF electrode.
130. The RF device of claim 127, wherein the sensor is positioned at the front surface of the RF electrode.
131. The RF device of claim 128, wherein the sensor detects a temperature of the front surface of the RF electrode.
132. The RF device of claim 122, further comprising:
a cooling member coupled to the support structure and configured to cool the back surface of the RF electrode.
a cooling member coupled to the support structure and configured to cool the back surface of the RF electrode.
133. The RF device of claim 132, wherein the cooling member is distanced from the back surface of the RF electrode.
134. The RF device of claim 132, wherein the cooling member is a thermo-electric cooler.
135. An RF device, comprising:
an RF electrode coupled including conductive and dielectric portions;
a support structure coupled to the RF electrode;
a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode, the support structure and the RF electrode forming a seal where the support structure is coupled to the RF electrode.
an RF electrode coupled including conductive and dielectric portions;
a support structure coupled to the RF electrode;
a cooling member coupled to the support structure and configured to cool a back surface of the RF electrode, wherein the cooling member is distanced from the back surface of the RF electrode, the support structure and the RF electrode forming a seal where the support structure is coupled to the RF electrode.
136. The RF device of claim 135, wherein the seal is a fluid tight seal.
137. An RF device, comprising:
an RF electrode including conductive and dielectric portions, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
an RF electrode including conductive and dielectric portions, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
138. The device of claim 137, wherein the voids are configured to reduce edge effects at an edge of the RF electrode.
139. The device of claim 137, wherein the voids are configured to affect at least one of depth, uniformity and shape of an electric field created by the RF
electrode.
electrode.
140. An RF device, comprising:
an RF electrode including conductive and dielectric portions, and a flex circuit, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
an RF electrode including conductive and dielectric portions, and a flex circuit, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
141. The device of claim 140, wherein are configured to reduce edge effects at an edge of the RF electrode.
142. The device of claim 140, wherein the voids are configured to affect at least one of depth, uniformity and shape of an electric field created by the RF
electrode.
electrode.
143. An RF device, comprising:
an RF electrode including conductive and dielectric portions, the dielectric portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
an RF electrode including conductive and dielectric portions, the dielectric portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
144. The device of claim 143, wherein are configured to reduce edge effects at an edge of the RF electrode.
145. The device of claim 143, wherein the voids are configured to affect at least one of depth, uniformity and shape of an electric field created by the RF
electrode.
electrode.
146. An RF device, comprising:
an RF electrode including conductive and dielectric portions, the RF electrode configured to be capacitively coupled when at least a portion of the RF
electrode is in contact with a skin surface, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
an RF electrode including conductive and dielectric portions, the RF electrode configured to be capacitively coupled when at least a portion of the RF
electrode is in contact with a skin surface, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface.
147. The device of claim 146, wherein are configured to reduce edge effects at an edge of the RF electrode.
148. The device of claim 146, wherein the voids are configured to affect at least one of depth, uniformity and shape of an electric field created by the RF
electrode.
electrode.
149. An RF device, comprising:
an RF electrode including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface, the conductive portion including voids, the dielectric portion being positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface; and at least a first sensor coupled to the RF electrode.
an RF electrode including conductive and dielectric portions, the RF electrode having a tissue interface surface and an opposing back surface, the conductive portion including voids, the dielectric portion being positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface; and at least a first sensor coupled to the RF electrode.
150. The device of claim 149, wherein the voids are configured to reduce edge effects at an edge of the RF electrode.
151. The device of claim 149, wherein the voids are configured to affect at least one of depth, uniformity and shape of an electric field created by the RF
electrode.
electrode.
152. An RF device, comprising:
a support structure an RF electrode coupled to the support structure and including conductive and dielectric portions, the conductive portion having voids; and first and second engagement members formed in the body of the support structure, the first and second engagement members providing engagement and disengagement with a handpiece support structure.
a support structure an RF electrode coupled to the support structure and including conductive and dielectric portions, the conductive portion having voids; and first and second engagement members formed in the body of the support structure, the first and second engagement members providing engagement and disengagement with a handpiece support structure.
153. The device of claim 152, wherein are configured to reduce edge effects at an edge of the RF electrode.
154. The device of claim 152, wherein the voids are configured to affect at least one of depth, uniformity and shape of an electric field created by the RF
electrode.
electrode.
155. A method of treatment, comprising:
providing an RF device with an RF electrode that has conductive and dielectric portions, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface;
delivering a charge to the RF electrode, wherein the voids affect at least one of depth, uniformity and shape of an electric field created by the RF electrode;
positioning the RF device with the dielectric portion positioned adjacent to the skin surface; and delivering RF energy from the RF device through the skin surface.
providing an RF device with an RF electrode that has conductive and dielectric portions, the conductive portion having voids and the dielectric portion positioned between the conductive portion and a skin surface when the RF electrode is positioned at the skin surface;
delivering a charge to the RF electrode, wherein the voids affect at least one of depth, uniformity and shape of an electric field created by the RF electrode;
positioning the RF device with the dielectric portion positioned adjacent to the skin surface; and delivering RF energy from the RF device through the skin surface.
156. The method of claim 155, further comprising:
cooling the skin surface.
cooling the skin surface.
157. A method for inducing the formation of scar collagen in a selected collagen containing tissue site beneath a skin surface, comprising:
providing an RF device with an RF electrode that has conductive and dielectric portions;
creating a reverse thermal gradient through the skin surface where a temperature of the skin surface is lower than the selected collagen containing tissue site;
and delivering energy from the RF device through the skin surface to the selected collagen containing tissue site for a sufficient time to induce collagen formation in the selected collagen containing tissue site, minimizing cellular necrosis of the skin surface and creating a tissue effect at the skin surface. 158. A method for inducing the formation of scar collagen in a selected collagen containing tissue site beneath a skin surface, comprising:
providing an RF device with an RF electrode that has conductive and dielectric portions;
delivering energy from the RF device through the skin surface to the selected collagen containing tissue site for a sufficient time to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface; and creating a tissue effect at the skin surface.
159. A method for inducing the formation of scar collagen in a selected collagen containing tissue site beneath a skin surface, comprising:
providing an RF device with an RF electrode that has conductive and dielectric portions and an energy delivery surface;
positioning the energy delivery surface on the skin surface;
creating a reverse thermal gradient through the skin surface sufficiently to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface, wherein a temperature of the skin surface is lower than the collagen containing tissue site; and creating a tissue effect at the skin surface.
160. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions;
creating a reverse thermal gradient through a skin surface where a temperature of the skin surface is lower than tissue underlying the skin surface; and delivering energy from the treatment apparatus through the skin surface to the tissue underlying the skin surface for a sufficient time to create a desired tissue effect while minimizing cellular necrosis of the skin surface.
161. The method of claim 160, wherein the tissue effect is dermal remodeling.
162. The method of claim 160, wherein the tissue effect is skin tightening.
163. The method of claim 160, wherein the tissue effect is wrinkle reduction.
164. The method of claim 160, wherein the tissue effect is elastosis reduction.
165. The method of claim 160, wherein the tissue effect is scar reduction.
166. The method of claim 160, wherein the tissue effect is hair follicle modification.
167. The method of claim 160, wherein the tissue effect is modification of contour irregularities of a skin surface.
168. The method of claim 160, wherein the tissue effect is a creation of scar or nascent collagen.
169. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions;
delivering energy from the treatment apparatus through a skin surface to a selected collagen containing tissue site for a sufficient time to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface;
modifying at least a portion of the skin surface.
170. The method of claim 169, wherein the treatment apparatus includes a light delivery device.
171. A method for creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions and an energy delivery surface;
coupling the energy delivery surface with an external surface of the skin;
creating a reverse thermal gradient through a surface of the skin while heating underlying collagen containing tissue, wherein a temperature of the external skin surface is lower than a temperature of the underlying collagen containing tissue;
delivering energy from the treatment apparatus through a skin surface to a selected collagen containing tissue site for a sufficient time to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface; and creating a desired tissue effect.
172. The method of claim 171, wherein the treatment apparatus includes a light delivery device.
173. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions and an energy delivery surface;
reducing a temperature of a collagen containing tissue site below a skin surface;
creating a thermal injury to at least a portion of the collagen in the collagen containing tissue site with a minimal cellular destruction in the skin surface; and inducing scar collagen formation.
174. The method of claim 173, wherein the treatment apparatus includes a light delivery device.
175. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions;
coupling the RF device with a skin surface;
creating a reverse thermal gradient through the skin surface to sufficiently heat an underlying collagen containing tissue, wherein a temperature of the skin surface is lower than a temperature of the underlying collagen containing tissue;
delivering energy from the treatment apparatus through the skin surface to the tissue underlying the skin surface for a sufficient time to induce scar collagen formation while minimizing cellular necrosis of the skin surface.
176. The method of claim 175, wherein the treatment apparatus includes a light delivery device.
177. The RF device of claim 42, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
178. The RF device of claim 42, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
179. The RF device of claim 45, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
180. The RF device of claim 45, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
181. The RF device of claim 88, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
182. The RF device of claim 88, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
183. The RF device of claim 91, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
184. The RF device of claim 91, wherein the lion-volatile memory is positioned at an RF energy source coupled to the RF electrode.
185. The RF device of claim 102, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
186. The RF device of claim 102, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
187. The RF device of claim 110, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
188. The RF device of claim 110, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
providing an RF device with an RF electrode that has conductive and dielectric portions;
creating a reverse thermal gradient through the skin surface where a temperature of the skin surface is lower than the selected collagen containing tissue site;
and delivering energy from the RF device through the skin surface to the selected collagen containing tissue site for a sufficient time to induce collagen formation in the selected collagen containing tissue site, minimizing cellular necrosis of the skin surface and creating a tissue effect at the skin surface. 158. A method for inducing the formation of scar collagen in a selected collagen containing tissue site beneath a skin surface, comprising:
providing an RF device with an RF electrode that has conductive and dielectric portions;
delivering energy from the RF device through the skin surface to the selected collagen containing tissue site for a sufficient time to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface; and creating a tissue effect at the skin surface.
159. A method for inducing the formation of scar collagen in a selected collagen containing tissue site beneath a skin surface, comprising:
providing an RF device with an RF electrode that has conductive and dielectric portions and an energy delivery surface;
positioning the energy delivery surface on the skin surface;
creating a reverse thermal gradient through the skin surface sufficiently to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface, wherein a temperature of the skin surface is lower than the collagen containing tissue site; and creating a tissue effect at the skin surface.
160. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions;
creating a reverse thermal gradient through a skin surface where a temperature of the skin surface is lower than tissue underlying the skin surface; and delivering energy from the treatment apparatus through the skin surface to the tissue underlying the skin surface for a sufficient time to create a desired tissue effect while minimizing cellular necrosis of the skin surface.
161. The method of claim 160, wherein the tissue effect is dermal remodeling.
162. The method of claim 160, wherein the tissue effect is skin tightening.
163. The method of claim 160, wherein the tissue effect is wrinkle reduction.
164. The method of claim 160, wherein the tissue effect is elastosis reduction.
165. The method of claim 160, wherein the tissue effect is scar reduction.
166. The method of claim 160, wherein the tissue effect is hair follicle modification.
167. The method of claim 160, wherein the tissue effect is modification of contour irregularities of a skin surface.
168. The method of claim 160, wherein the tissue effect is a creation of scar or nascent collagen.
169. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions;
delivering energy from the treatment apparatus through a skin surface to a selected collagen containing tissue site for a sufficient time to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface;
modifying at least a portion of the skin surface.
170. The method of claim 169, wherein the treatment apparatus includes a light delivery device.
171. A method for creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions and an energy delivery surface;
coupling the energy delivery surface with an external surface of the skin;
creating a reverse thermal gradient through a surface of the skin while heating underlying collagen containing tissue, wherein a temperature of the external skin surface is lower than a temperature of the underlying collagen containing tissue;
delivering energy from the treatment apparatus through a skin surface to a selected collagen containing tissue site for a sufficient time to induce a formation of new collagen in the selected collagen containing tissue site with no deeper than a second degree burn created on the skin surface; and creating a desired tissue effect.
172. The method of claim 171, wherein the treatment apparatus includes a light delivery device.
173. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions and an energy delivery surface;
reducing a temperature of a collagen containing tissue site below a skin surface;
creating a thermal injury to at least a portion of the collagen in the collagen containing tissue site with a minimal cellular destruction in the skin surface; and inducing scar collagen formation.
174. The method of claim 173, wherein the treatment apparatus includes a light delivery device.
175. A method of creating a tissue effect, comprising:
providing a treatment apparatus that includes providing an RF device with an RF
electrode that has conductive and dielectric portions;
coupling the RF device with a skin surface;
creating a reverse thermal gradient through the skin surface to sufficiently heat an underlying collagen containing tissue, wherein a temperature of the skin surface is lower than a temperature of the underlying collagen containing tissue;
delivering energy from the treatment apparatus through the skin surface to the tissue underlying the skin surface for a sufficient time to induce scar collagen formation while minimizing cellular necrosis of the skin surface.
176. The method of claim 175, wherein the treatment apparatus includes a light delivery device.
177. The RF device of claim 42, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
178. The RF device of claim 42, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
179. The RF device of claim 45, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
180. The RF device of claim 45, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
181. The RF device of claim 88, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
182. The RF device of claim 88, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
183. The RF device of claim 91, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
184. The RF device of claim 91, wherein the lion-volatile memory is positioned at an RF energy source coupled to the RF electrode.
185. The RF device of claim 102, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
186. The RF device of claim 102, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
187. The RF device of claim 110, wherein the non-volatile memory is positioned at the support structure or the RF electrode.
188. The RF device of claim 110, wherein the non-volatile memory is positioned at an RF energy source coupled to the RF electrode.
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-
2003
- 2003-03-25 US US10/397,976 patent/US7452358B2/en not_active Expired - Fee Related
-
2004
- 2004-03-25 AU AU2004226484A patent/AU2004226484B2/en not_active Expired
- 2004-03-25 BR BRPI0409026-8A patent/BRPI0409026A/en not_active IP Right Cessation
- 2004-03-25 CN CNB2004800112228A patent/CN100425211C/en not_active Expired - Lifetime
- 2004-03-25 CA CA002519304A patent/CA2519304A1/en not_active Abandoned
- 2004-03-25 EP EP04758313A patent/EP1613233A4/en not_active Withdrawn
- 2004-03-25 JP JP2006509276A patent/JP2006521178A/en active Pending
- 2004-03-25 KR KR1020057017812A patent/KR20050114676A/en not_active Application Discontinuation
- 2004-03-25 WO PCT/US2004/009118 patent/WO2004087253A2/en active Application Filing
Also Published As
Publication number | Publication date |
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JP2006521178A (en) | 2006-09-21 |
US7452358B2 (en) | 2008-11-18 |
AU2004226484B2 (en) | 2009-03-26 |
AU2004226484A1 (en) | 2004-10-14 |
US20030216728A1 (en) | 2003-11-20 |
CN1780588A (en) | 2006-05-31 |
AU2004226484A2 (en) | 2004-10-14 |
WO2004087253A2 (en) | 2004-10-14 |
WO2004087253A3 (en) | 2004-12-29 |
CN100425211C (en) | 2008-10-15 |
KR20050114676A (en) | 2005-12-06 |
BRPI0409026A (en) | 2006-03-28 |
EP1613233A4 (en) | 2007-08-29 |
EP1613233A2 (en) | 2006-01-11 |
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