CA2362276A1 - Systems and methods for shrinking collagen in the dermis - Google Patents
Systems and methods for shrinking collagen in the dermis Download PDFInfo
- Publication number
- CA2362276A1 CA2362276A1 CA002362276A CA2362276A CA2362276A1 CA 2362276 A1 CA2362276 A1 CA 2362276A1 CA 002362276 A CA002362276 A CA 002362276A CA 2362276 A CA2362276 A CA 2362276A CA 2362276 A1 CA2362276 A1 CA 2362276A1
- Authority
- CA
- Canada
- Prior art keywords
- electrodes
- electromagnetic energy
- carrier
- tissue
- epidermal
- 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
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/148—Probes or electrodes therefor having a short, rigid shaft for accessing the inner body transcutaneously, e.g. for neurosurgery or arthroscopy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00743—Type of operation; Specification of treatment sites
- A61B2017/00747—Dermatology
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
- A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
- A61B2018/00023—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00059—Material properties
- A61B2018/00071—Electrical conductivity
- A61B2018/00083—Electrical conductivity low, i.e. electrically insulating
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00452—Skin
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00702—Power or energy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00791—Temperature
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1405—Electrodes having a specific shape
- A61B2018/1425—Needle
- A61B2018/143—Needle multiple needles
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1472—Probes or electrodes therefor for use with liquid electrolyte, e.g. virtual electrodes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1497—Electrodes covering only part of the probe circumference
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
- A61B2018/1861—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves with an instrument inserted into a body lumen or cavity, e.g. a catheter
Abstract
Devices are specially configured to apply electromagnetic energy to skin. Each device comprises a carrier (30), and an array of electrodes (58) on the carrier, which are connected to a source of electromagnetic energy. The carrier, in use, contacts epidermal tissue (16). The electrodes either rest on the epidermal surface, or alternatively, are sized to extend into tissue beneath the epidermal tissue, e.g., into dermal tissue or into subdermal tissue. The carrier can be differently shaped to match different skin region topographies.
Description
_ 1 _ SYSTEMS AND METHODS FOR
SHRINKING COLLAGEN IN THE DERMIS
FIELD OF THE INVENTION
In a general sense, the invention is directed to systems and methods for treating cosmetic conditions in the human body. In a more particular sense, the invention is directed to systems and methods for treating cosmetic conditions affecting the skin of the face and neck, as evidenced by the appearance of lines and wrinkles in the face, or neck, or both.
BACKGROUND OF THE INVENTION
The skin is the principal seat of the sense of touch. The skin also provides protection against the physical forces of the environment, such as heat, cold, sun rays, friction, pressure, and chemicals.
Exposure of the skin to these environmental forces can, over time, cause the skin to sag or wrinkle. Hyperfunctional nervous disorders and normal contraction of facial and neck muscles, e.g.
by frowning or squinting, can also over time form furrows or bands in the face and neck region. These and other effects of the normal aging process can present an aesthetically unpleasing cosmetic appearance.
Accordingly, there is a large demand for systems and methods which serve to "tighten" the skin to remove sags and wrinkles in the face and neck.
SHRINKING COLLAGEN IN THE DERMIS
FIELD OF THE INVENTION
In a general sense, the invention is directed to systems and methods for treating cosmetic conditions in the human body. In a more particular sense, the invention is directed to systems and methods for treating cosmetic conditions affecting the skin of the face and neck, as evidenced by the appearance of lines and wrinkles in the face, or neck, or both.
BACKGROUND OF THE INVENTION
The skin is the principal seat of the sense of touch. The skin also provides protection against the physical forces of the environment, such as heat, cold, sun rays, friction, pressure, and chemicals.
Exposure of the skin to these environmental forces can, over time, cause the skin to sag or wrinkle. Hyperfunctional nervous disorders and normal contraction of facial and neck muscles, e.g.
by frowning or squinting, can also over time form furrows or bands in the face and neck region. These and other effects of the normal aging process can present an aesthetically unpleasing cosmetic appearance.
Accordingly, there is a large demand for systems and methods which serve to "tighten" the skin to remove sags and wrinkles in the face and neck.
One prior method surgically resurfaces facial skin by ablating the outer layer of the skin (from 200 ~Cm to 600 Vim), using laser or chemicals.
In time, a new skin surface develops. The laser and chemicals used to resurface the skin also irritate or heat collagen tissue, which is widely present in the dermis. When irritated or heated in prescribed ways, the collagen tissue partially dissociates and, in doing so, shrinks. The shrinkage of collagen also leads to a desirable "tightened" look. Still, laser or chemical resurfacing leads to prolonged redness of the skin, infection risk, increased or decreased pigmentation, and scarring.
Lax et al. US 5,458,596 describes the use of radio frequency energy to shrink collagen tissue.
This cosmetically beneficial effect can be achieved in facial and neck areas of the body in a minimally intrusive manner, without requiring the surgical removal of the outer layers of skin and the attendant problems just listed.
SUMMARY OF THE INVENTION
The invention provides improved systems and methods of systems and methods of achieving the cosmetically beneficial effects of shrinking collagen tissue in the dermis in an effective, non-invasive manner, which leaves the outer layer of skin intact and undamaged.
One aspdct of the invention provides systems and methods for applying electromagnetic energy to skin. The systems and methods include a carrier and an array of electrodes on the carrier, which are connectable to a source of electromagnetic energy to apply the electromagnetic energy.
According to this aspect of the invention, a microporous pad on the carrier overlays the array of electrodes, forming an interior chamber to contain an electrically conductive material. The microporous pad is adapted, in use, to contact an epidermal skin region and ionically transport the applied electromagnetic energy to ohmically heat dermal tissue beneath the epidermal skin region.
In one embodiment, the shape of the carrier can differ to match different skin region topographies.
Another aspect of the invention provides systems and methods for applying electromagnetic energy to skin, in which the array of electrodes on the carrier are sized so that, while the carrier contacts an epidermal skin region, the electrodes extend into tissue beneath the epidermal skin region to ohmically heat dermal tissue.
In one embodiment, the electrodes are sized to extend into dermal tissue. In another embodiment, the electrodes are sized to extend into subdermal tissue.
In one embodiment, the shape of the carrier can differ to match different skin region topographies.
Another aspect of the invention provides systems and methods for applying electromagnetic energy to a facelift flap. The systems and methods include a carrier and at least one electrode on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy. The electrode is sized so that, while the carrier contacts a backside of the flap, the electrode ohmically heats the dermal tissue.
In one embodiment, the electrode, in use, rests on a surface on the backside of the flap.
In another embodiment, the electrode is sized to extend into dermal tissue within the flap.
Another aspect of the invention provides a family of devices for applying electromagnetic energy to skin. Each device comprising a carrier having a shape and an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy.
According to this aspect of the invention, the shapes of the carriers differ to match different skin region topographies.
In one embodiment, the carrier is adapted, in use, to contact epidermal tissue. In this embodiment, the electrodes are sized to extend into tissue beneath the epidermal tissue. The electrodes can be sized to extend into dermal tissue.
Alternatively, the electrodes are sized to extend into subdermal tissue.
Features and advantages of the inventions are set forth in the following Description and Drawings, as well as in the appended Claims.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is a representative side section view of skin and underlying subcutaneous tissue;
Fig. 2 is a schematic view of a system that, in use, heats collagen tissue in the dermis for the purpose of treating cosmetic conditions affecting the skin;
Fig. 3 is an exploded perspective view of one category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy into the dermis externally through the epidermis;
Fig. 4 is a side section view of the energy applicator shown in Fig. 3 in use to heat collagen tissue in the dermis;
In time, a new skin surface develops. The laser and chemicals used to resurface the skin also irritate or heat collagen tissue, which is widely present in the dermis. When irritated or heated in prescribed ways, the collagen tissue partially dissociates and, in doing so, shrinks. The shrinkage of collagen also leads to a desirable "tightened" look. Still, laser or chemical resurfacing leads to prolonged redness of the skin, infection risk, increased or decreased pigmentation, and scarring.
Lax et al. US 5,458,596 describes the use of radio frequency energy to shrink collagen tissue.
This cosmetically beneficial effect can be achieved in facial and neck areas of the body in a minimally intrusive manner, without requiring the surgical removal of the outer layers of skin and the attendant problems just listed.
SUMMARY OF THE INVENTION
The invention provides improved systems and methods of systems and methods of achieving the cosmetically beneficial effects of shrinking collagen tissue in the dermis in an effective, non-invasive manner, which leaves the outer layer of skin intact and undamaged.
One aspdct of the invention provides systems and methods for applying electromagnetic energy to skin. The systems and methods include a carrier and an array of electrodes on the carrier, which are connectable to a source of electromagnetic energy to apply the electromagnetic energy.
According to this aspect of the invention, a microporous pad on the carrier overlays the array of electrodes, forming an interior chamber to contain an electrically conductive material. The microporous pad is adapted, in use, to contact an epidermal skin region and ionically transport the applied electromagnetic energy to ohmically heat dermal tissue beneath the epidermal skin region.
In one embodiment, the shape of the carrier can differ to match different skin region topographies.
Another aspect of the invention provides systems and methods for applying electromagnetic energy to skin, in which the array of electrodes on the carrier are sized so that, while the carrier contacts an epidermal skin region, the electrodes extend into tissue beneath the epidermal skin region to ohmically heat dermal tissue.
In one embodiment, the electrodes are sized to extend into dermal tissue. In another embodiment, the electrodes are sized to extend into subdermal tissue.
In one embodiment, the shape of the carrier can differ to match different skin region topographies.
Another aspect of the invention provides systems and methods for applying electromagnetic energy to a facelift flap. The systems and methods include a carrier and at least one electrode on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy. The electrode is sized so that, while the carrier contacts a backside of the flap, the electrode ohmically heats the dermal tissue.
In one embodiment, the electrode, in use, rests on a surface on the backside of the flap.
In another embodiment, the electrode is sized to extend into dermal tissue within the flap.
Another aspect of the invention provides a family of devices for applying electromagnetic energy to skin. Each device comprising a carrier having a shape and an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy.
According to this aspect of the invention, the shapes of the carriers differ to match different skin region topographies.
In one embodiment, the carrier is adapted, in use, to contact epidermal tissue. In this embodiment, the electrodes are sized to extend into tissue beneath the epidermal tissue. The electrodes can be sized to extend into dermal tissue.
Alternatively, the electrodes are sized to extend into subdermal tissue.
Features and advantages of the inventions are set forth in the following Description and Drawings, as well as in the appended Claims.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is a representative side section view of skin and underlying subcutaneous tissue;
Fig. 2 is a schematic view of a system that, in use, heats collagen tissue in the dermis for the purpose of treating cosmetic conditions affecting the skin;
Fig. 3 is an exploded perspective view of one category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy into the dermis externally through the epidermis;
Fig. 4 is a side section view of the energy applicator shown in Fig. 3 in use to heat collagen tissue in the dermis;
Fig. 5 is a front view of the facial and neck region showing various energy applicator, like that shown in Fig. 3, specially shaped to match the topography of a skin region under the eye, below the ear, under the chin, around the lips, and on the forehead above the eyebrows;
Fig. 6 is an exploded perspective view of another category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy internally directly into the dermis;
Fig. 7 is a side section view of the energy applicator shown in Fig. 6 in use to heat collagen tissue in the dermis;
Fig. 8 is an exploded perspective view, with portions in section, of another category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy into the dermis internally through subcutaneous tissue;
Fig. 9 is a side section view of the energy applicator shown in Fig. 8 in use to heat collagen tissue in the dermis;
Fig. 10 is an exploded, perspective view of another category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy into the dermis from the backside of a surgically created facelift flap.
Fig. 11 is a side section view of the energy applicator shown in Fig. 10 in use to heat collagen tissue in the dermis from the backside of a facelift flap;
Fig. 12 is a perspective view of an energy applicator of the type shown in Fig. 3, with associated probes for sensing temperature in the dermis;
Fig. 13 is a side section view of an energy applicator shown in Fig. 3, with the sensors deployed in the dermis to sense temperature conditions;
Fig. 14 is a side section view of an energy applicator of the type shown in Fig. 6, with associated sensors located in the dermis to sense temperature conditions; and Fig. 15 is a side section view of a penetration tissue temperature sensing probe of the type shown in Figs. 12 to 14, with multiple sensors deployed in a stacked arrangement to sense a temperature gradient in the dermis.
The invention may be embodied in several forms without departing from its spirit or essential characteristics. The scope of the invention is defined in the appended claims, rather than in the specific description preceding them. All embodi-ments that fall within the meaning and range of equivalency of the claims are therefore intended to be embraced by the claims.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
The invention provides systems and methods of treating cosmetic conditions affecting the skin.
The system and methods are applicable for use throughout the body. However, the systems and methods are particularly well suited for treating cosmetic conditions in the facial or neck area of the body. For this reason, the systems and methods will be described in this context.
I. Anatomy of the Skin As Fig. 1 shows, the skin 10 overlies and protects subcutaneous tissue 12 and muscle tissue 14 of the body. In the face and neck areas, the skin 10 measures about 2mm in cross section.
The skin 10 includes an external, non-_ 7 _ vascular covering of epithelial cells, called the epidermis 16. In the face and neck regions, the epidermis measures about 100 ~,m in cross section.
The skin 10 also includes a layer of vascular tissue, named the dermis 18. In the face and neck regions, the dermis 18 measures about 1900 ~cm in cross section.
The dermis 18 is tough, flexible, and highly elastic. It is divided into a papillary (upper) layer 20 and a reticular (lower) layer 22.
The most numerous fibers in the papillary and reticular layers 20 and 22 are collagen fibers, which in large part account for the strength and physical properties of the dermis 18. Hair bulbs, sweat ducts, and other glands also occupy the reticular layer 22.
The f fibrous structure of collagen tissue is observed to dissociate and contract along its length when heated to a defined temperature condition, i.e., about 65 ~C. The contraction of collagen tissue causes the dermis 18 to reduce in size, which has an observable tightening effect. As collagen contacts, wrinkles and sag lines in the skin are ameliorated. As a result, the outward cosmetic appearance of the skin 10 improves.
The temperature conditions conducive to the beneficial results of collagen shrinkage lay well above the temperature conditions at which irreversible thermal damage to epithelial cells begins to occur, i.e., above about 47~ C.
II. systems for Renovating the Dermis A. System overview Fig. 2 shows a system 24 for renovating and reconstituting the dermis. The system 24 applies energy to the dermis to elevate and maintain its _ g _ temperature at a predetermined temperature condition, at or about 65Q C, without increasing the temperature of the epidermis beyond 47Q C. In this way, the system applies energy to the dermis in a targeted, selective fashion, to dissociate and contract collagen tissue, while preserving and protecting epithelial cells against thermal damage.
The system 24 includes a treatment device 26. The device 26 includes a handle 28 made, e.g., from molded plastic. The handle 28 carries at its distal end a treatment energy applicator 30, which, in use, contacts the epidermis. The handle 28 is sized to be conveniently grasped like a pencil or paint brush by a physician, to thereby manipulate the applicator 30 on the epidermis 16.
The system 24 further includes a device 32 to generate treatment energy. In the illustrated embodiment, the generator 32 generates radio frequency energy, e.g., having a frequency in the range of about 400 kHz to about 10 mHz.
A cable 34 extending from the proximal end of the handle 28 terminates with an electrical connector 36. The cable 34 is electrically coupled to the applicator 30, e.g., by wires that extend through the interior of the handle 28. When connector 36 plugs into the generator 32, to convey the generated energy to the applicator 30 for transmission to the skin.
The system 24 also includes certain auxiliary processing equipment 38 and 40. In the illustrated embodiment, the processing equipment 38 comprises an external fluid delivery apparatus, and the processing equipment 40 comprises an external aspirating apparatus.
The handle 28 of the treatment device 26 g includes one or more interior lumens 42. The lumens terminate in fittings 44 and 46, located at the proximal end of the handle 28. One fitting 44 connects to the fluid delivery apparatus 38, to convey processing fluid to the distal end of the handle 28 for discharge. The other fitting 46 connects to the aspirating apparatus 40, to convey aspirated material from the distal end of the handle 28 for discharge.
The system 24 also includes a controller 48. The controller 48, which preferably includes a central processing unit (CPU), is linked to the generator 32, the fluid delivery apparatus 38, and the aspirating apparatus 40. The controller 48 governs the power levels, cycles, and duration that the radio frequency energy is distributed to the applicator 30, to achieve and maintain power levels appropriate to achieve the desired treatment objectives. In tandem, the controller 48 also governs the delivery of processing fluid to the applicator 30 and the removal of aspirated material from the applicator 30.
The controller 48 includes an input/output (I/O) device 50.. The I/0 device 50 allows the physician to input control and processing variables, to enable the controller 48 to generate appropriate command signals. The I/O device 50 also receives real time processing feedback information from one or more sensors 52 associated with the applicator, for processing by the controller 48, e.g., to govern the application of energy and the delivery of processing fluid. The I/O device 50 also includes a display 54, to graphically present processing information to the physician for viewing or analysis.
H. The Treatment Device The ,structure of the treatment device 26 and associated electrical energy applicator 30 can vary.
The illustrated embodiments describe and show four representative categories of energy applicators 30, as follows:
(i) a first category applicator 30(1) (shown in Figs. 3 and 4) transmits energy into the dermis externally through the epidermis.
(ii) a second category applicator 30(2) (shown in Figs. 6 and 7) transmits energy internally directly into the dermis.
(iii) a third category applicator 30(3)(shown in Figs. 8 and 9) transmits energy into the dermis internally through subcutaneous tissue.
(iv) a fourth category applicator 30(4)(shown in Figs. 1o and 11) transmits energy into the dermis from the backside of a surgically created facelift flap.
The various categories of energy applicators 30(1), 30(2), 30(3), and 30(4) will now be discussed in greater detail.
(i). Epidermal Energy Applicator In this category, as shown in Fig. 3, the energy applicator 30(1) includes a carrier grid 56, which is mounted on the distal end of the handle 28.
The carrier grid 56 is made from an electrically non-conducting material, e.g., plastic or ceramic.
The carrier grid 56 carries a pattern of multiple, spaced apart electrodes 58. Each electrode 58 comprises a discrete transmission source of radio frequency energy. The electrodes 58 can be made, e.g., from stainless steel, platinum, and other noble metals, or combinations thereof. The electrodes 58 may be fastened to the grid by various means, e.g., by adhesives, by painting, or by other coating or deposition techniques.
In the illustrated embodiment, the carrier grid 56 is formed by an outside frame 60 with crossing interior spacers 62. Together, the frame 60 and spacers 62 define an open lattice of cells 64.
In the illustrated embodiment, the grid 56 defines sixteen cells 64. It should be appreciated that the cells 64 could number more or less than sixteen.
In the illustrated embodiment, the electrodes 58 are located on the grid 56 at the four corners of each cell 64. This arrangement provides a symmetric pattern of twenty-five electrodes 58 on the grid 56. Still, it should be appreciated that the electrodes 58 could be arranged in other symmetric or non-symmetric patterns in the grid.
In the embodiment shown in Fig. 3, the energy applicator 30(1) includes an external pad 66, which is attached peripherally about the carrier grid 56. The pad 66 is made from a resilient microporous membrane. As Fig. 4 shows, the pad 66, in use, makes surface contact with the epidermis 16.
The resilience of the pad 66 makes it well suited to conform to a variable surface topography of the epidermis 16.
The attachment of the pad about the carrier grid 56 creates an interior chamber 68, which encloses the grid 56. The applicator 30(1) further includes a fluid manifold 70 inside the chamber 68.
The fluid manifold 70 communicates with the fluid delivery apparatus 38, via the handle lumens 42.
The manifold 70 uniformly introduces processing fluid through the grid 56 and into the interior chamber 68.
In this arrangement, the processing fluid comprises an electrically conductive liquid, such as saline (about 0.9% to 3.0%). The apparatus 38 includes a pump 72 to convey the electrically conductive liquid through the manifold 70 at a prescribed rate.
The flow of the electrically conductive liquid into the through the grid 56 and into interior chamber 68 contacts the interior surface of the microporous membrane of the pad 66. As Fig. 4 shows, the microporous membrane of the pad 66 has pores 74 sized to permit passage of the electrically conductive fluid in the chamber 68 through the membrane and into contact with the epidermis 16 the membrane contacts.
The diffusion. of electrically conductive liquid through the membrane pores 74 serves two purposes. First, it creates conductive cooling at the interface between the membrane pad 66 and the epidermis 16. Second, it serves to ionically transport radio frequency energy transmitted by the grid electrodes 58 through the membrane pores 74, for return (in a unipolar arrangement) through exterior patch electrode 76 coupled to patient ground.
The ionically conducted radio frequency energy transported through the membrane pore 74 will, in turn, cause localized ohmic heating of skin tissue. The application of radio frequency energy by ionic transport to the epidermis surface, simultaneously combined with the conductive surface cooling effects that the ionic transport also provides, places the tissue region where maximum temperature conditions exist (designated TMAX in Fig. 4) at a location below the epidermis 16, into the papillary dermis 20 and, preferably, into the reticular dermis 22 as well.
The applicator 30(1) thereby makes possible selective heating of the interior dermis 18 to a maximum tissue temperature TMAX of about 65QC, while maintaining the temperature of the epidermis 16 at or about 20QC to 30QC, thereby avoiding thermal damage to the epidermis 16.
Alternatively, an electrically conductive jelly can occupy the interior chamber 68. The jelly causes ionic transport of radio frequency energy through the membrane pores 74. In this arrangement, a manifold 78 distributes fluid about the periphery of the pad 66, but not into the chamber 68 itself, to nevertheless cause connective surface cooling effects. In this arrangement, the fluid distributed by the manifold 78 need not be electrically conductive, but it can be to provide uniform distribution of the radio frequency energy at the pad 66.
In use, the physician places the pad 66 upon a targeted region of tissue. The controller 48 governs the application of radio frequency energy to the electrodes 58 in concert with the delivery of fluid to the manifold 70 (or 78), to control the desired epidermal and dermal tissue temperature conditions. The controller 48 can also govern the withdrawal of fluid from the vicinity of the pad 66 through the aspirating apparatus 40 for this purpose. The controller 48 can alter the distribution of the radio frequency energy among selected sets or subsets of one or more grid electrodes 58. In this way, the controller 48 can focus the application of radio frequency in selected patterns.
In maintaining control of the process, the controller 48 can depend upon empirically determined or modeled relationships among selected processing variables, including, e.g., tissue temperature, time, power, and fluid delivery rate, without actual temperature sensing. Preferably, however, localized tissue temperature conditions are sensed to provide direct feedback control, as will be described in greater detail later.
In the illustrated embodiment, the handle 28 and grid 56 can comprise reusable components. In this arrangement, the energy applicator pad 66 can comprise a single use component that is temporarily fastened to the handle 28 at time of use, e.g., by a conventional snap-fit, and then removed after use for disposal.
The pad 66 need not be sized to cover a targeted facial or neck region in its entirety.
Instead, the physician can locate the pad 66 in contact with a localized area of epidermal tissue within a targeted region. After applying the desired amount of radio frequency energy, the physician can relocate the pad 66 to an adjacent tissue area in the targeted region and again apply radio frequency energy. The physician can repeat this successive process, until the entire targeted region has been subject to treatment by exposure to radio frequency energy.
The energy applicator pads 66 can be specially shaped and contoured to provide different geometries, selected to match the topography of the targeted facial or neck region, e.g., under the eye (as pad 66(1) in Fig. 5 shows); or below the ear (as pad 66 ( 2 ) in Fig . 5 shows ) ; or under the chin ( as pad 66(3) in Fig. 5 shows); or around the lips (as pad 66(4) in Fig. 5 shows); or on the forehead above the eyebrows (as pad 66(5) in Fig. 5 shows).
(ii). Intradermal Energy Applicator As shown in Fig. 6, the second category of energy applicator 30(2) includes a carrier 80 on the distal end of the handle 28. The carrier 80 supports an array of spaced-apart needle electrodes 82. The electrodes 82 are metallic, being made, e.g., from stainless steel, platinum, other noble metals, or combinations thereof. Each electrode 82 comprises a discrete transmission source of radio frequency energy, which the controller 48 governs.
The carrier 80 can provide physical connections between control wires and each electrode 82, e.g., by solder or adhesive. Alternatively, the carrier 80 can have painted, coated, or otherwise deposited solid state circuitry to provide the electrical paths. The solid state circuitry can include a fuse element that interrupts electrical contact after a specified period of use, to thereby discourage reuse of the carrier 80.
In use (as Fig. 7 shows), the electrodes 82 are intended to be inserted as a unit on the carrier 80 through the epidermis 16 and into the dermis 18.
After insertion, the controller 48 conditions the electrodes 82 for operation in a unipolar mode. In this mode, energy transmitted by one or more of the electrodes 82 is returned by an indifferent patch electrode 84, which is coupled to patient ground.
Alternatively, the controller 48 can condition pairs of electrodes 82 to operate in a bipolar mode, with one electrode serving to transmit radio frequency energy, and the other electrode serving as the return path.
WO 00/48644 PCT/iJS00/02778 The size and spacing of the electrodes 82 shown in Figs. 10 and 11 are purposely set to penetrate the skin to a depth sufficient to pass entirely through the epidermis 16 and penetrate the papillary and, preferable, extend into the reticular dermis (e.g., about 200 ~m to 300 Vim). When used for this purpose, the electrodes 82 each possesses a total length of about 0.5 to about 3.0 mm. The electrodes are mutually spaced apart by about 0.5 mm to 10.0 mm.
An electrical insulating material 86 surrounds the proximal end of each electrode 82 by at least 0.5 mm. This leaves an exposed, non-insulated length at the distal end of about 0.5 mm to 2.5 mm. The insulating material 82 insulates the epidermis 16 and a portion of the dermis 18 from direct exposure to radio frequency energy transmitted by the exposed distal end.
The ratio between exposed and insulated regions on the electrodes 82 affects the impedance of the electrodes 82 during use. Generally speaking, the larger the exposed region is compared to the insulated region, a larger impedance value can be expected.
In use, the physician places the carrier 80 upon a desired region of tissue. The physician applies light pressure on the handle 28 to insert the needle electrodes 82 through the epidermis 16 and into the dermis 18. The controller 48 governs the application of radio frequency energy to the electrodes 82 to ohmically heat adjacent dermal tissue. The electrodes 82 can be operated individually or in groups to form defined energy application patterns. As before described, the controller 48 can depend upon the empirically determined or modeled relationships among processing variables to affect process control, with or without actual temperature sensing.
In this arrangement, the handle 28 can comprise a reusable component, and the carrier 80 with electrodes 82 can comprise a single use component, which is temporarily fastened to the distal end of the handle 28 for use and then removed after use for disposal.
As with the pad 66, the carrier 80 need not be sized to cover a targeted facial or neck region in its entirety. Instead, the physician can successive locate the carrier 80 in a localized areas within a targeted region, and apply radio frequency energy to each localized area.
Like the pad 66, the carrier 80 can also be specially shaped and contoured to provide different geometries, selected to match the topography of the targeted facial or neck region, as shown in Fig. 5.
(iii) Subdermal Energy Applicator As shown in Fig. 8, the third category of energy applicator 30(3) includes a carrier 88 mounted on the distal end of the handle 28. Like the carrier 80 shown in Fig. 6, the carrier 88 shown in Fig. 8 holds an array of spaced-apart, metallic needle electrodes 90. Each electrode 90 comprises a discrete transmission source of radio frequency energy, which the controller 48 governs.
As before explained, the carrier 88 can provide physical connections between control wires and each electrode 90, or carry painted, coated, or otherwise deposited solid state circuitry to provide the electrical paths.
As Fig. 9 best shows, the needle electrodes 90 shown in Fig. 8 differ from the electrode 82 in Fig. 6 in that they are longer than the needle electrodes 82. The longer electrodes 90 are intended to be inserted as a unit through both the epidermis 16 and the dermis 18, and extend into the subcutaneous tissue region 12 a short distance beyond the reticular dermis 22.
For this purpose, the electrodes 90 each possesses a total length of about 3.0 mm to 10.0 mm.
The electrodes 90 are mutually spaced apart by about 0.5 mm to 3.0 mm. An electrical insulating material 92 surrounds the proximal end of each electrode 90 by at least 2.0 mm. This leaves an exposed, non-insulated length at the distal end of each electrode 90 of about 3.0 mm to 4.0 mm. The insulating material 92 insulates the epidermis 16 and dermis 18 from direct exposure to radio frequency energy transmitted by the exposed distal ends of the electrodes 90.
In the illustrated embodiment, at least some, and preferably all, of the needle electrodes 90 include interior fluid passages 94 (see Fig. 8).
A manifold 96 couples a select number of the passages 94 in communication with the fluid delivery apparatus 38. This way, processing fluid can be introduced through the electrodes 90 and into the subcutaneous tissue surrounding the distal ends of the electrodes 90. The manifold 96 couples other passages 94 in communication with the aspirating device 40, to evacuate material through the distal ends of the electrodes 90.
In this embodiment, the processing fluid comprises an electrically conductive liquid, such as saline. The apparatus 38 includes a pump 72 (see Fig. 1) to convey the electrically conductive liquid to the manifold 96 at a prescribed rate. The manifold 96 disperses the electrically conductive liquid through the selected passages 94.
The controller conditions the electrodes 90 to operate in a unipolar mode. Energy transmitted by one or more of the electrodes 90 is returned by an indifferent patch electrode 100, which is coupled to patient ground (see Fig. 9). At the same time, electrically conductive liquid flows through the selected passages 94 into the surrounding subcutaneous tissue region 12 (shown by arrows 122 in Fig. 9), while liquid and other material is evacuated through the other passages 94 by the aspirating device 40 (as shown by arrows 124 in Fig.
9) .
The radio frequency energy transmitted by the exposed, distal ends of the electrodes 90 will cause localized ohmic heating of subcutaneous tissue. The conduction of the electrically conductive fluid ionically distributes the radio frequency energy in a uniform manner, while also providing a localized cooling effect. The cooling effect places the tissue region where maximum temperature conditions exist at a location (designated TMAX in Fig. 9) spaced from the distal ends of the electrodes 90, which includes the reticular dermis 22.
The localized heating effects will all cause fat tissue 102 in the subcutaneous tissue 12 to flow (see Fig. 9). Suction applied by the aspirating device 40 through the passages 94 can be used to evacuate flowing fat tissue from subcutaneous tissue 12 (as arrows 124 in Fig. 9 show). This provides localized liposuction effects in the subcutaneous region 12, in tandem with collagen heating effects in the dermis 18.
In use, the physician places the carrier 88 upon a desired region of tissue. The physician applies light pressure on the handle 18 to insert the needle electrodes 90 through the epidermis 16 and dermis 18 and into a subcutaneous tissue region 12. The controller 48 governs the application of radio frequency energy to the electrodes 90, which can be operated individually or in deffined patterns.
The carrier 88 need not be sized to cover an entire targeted region. The physician can locate the carrier 88 in successive local areas within a targeted region, and apply radio frequency energy to each localized area. Like the pad 66, the carrier 88 can also be specially shaped and contoured to provide different geometries, selected to match the topography of the targeted facial or neck region, as shown in Fig. 5.
As before described, the controller 48 can depend upon the empirically determined or modeled relationships among processing variables to affect process control, with or without actual temperature sensing.
In this embodiment, as in the preceding embodiment, the handle 28 can comprise a reusable component, and the carrier 88 and needle electrodes 90 can comprise a single use component that is temporarily fastened to the handle 28 for use and then removed after use for disposal.
(iv) Facelift Flap Energy Applicator As shown in Fig. 10, the fourth category of energy applicator 30(4) likewise includes a carrier 104 on the distal end of the handle 28. The carrier 104 holds a pair of bipolar metallic electrodes 106.
In use, energy transmitted by one of the electrodes - 21 °
106 is returned by the other electrode 106 to patient ground. Alternatively, the carrier 104 can hold an array of several needle electrodes, which are operated in either a bipolar or unipolar mode.
In use (see Fig. 11), the physician surgically creates a facelift flap 108 in the targeted tissue region. The flap 108 extends well into the dermis 18 (e.g., 200 ,gym to 300 Vim). The physician inserts the needle electrodes 106 into the backside of the flap 108 and applies radio frequency energy.
The size and spacing of the electrodes 106 are purposely set to penetrate into the backside of the skin flap 108 to a depth sufficient to locate the distal ends of the electrodes 106 in dermal tissue.
When used for this purpose, the electrodes 106 each possesses a total length of about 3.0 mm to 8.0 mm. The electrodes 106 are mutually spaced apart by about 0.5 mm to 10.0 mm.
Alternatively, in this embodiment, the applicator 30(4) can comprise an array of surface electrodes 106 that do not penetrate the skin flap 108, but which rest on the surface of the backside of the skin flap.
As before described, the controller 48 governs application of radio frequency energy to achieve the desired tissue effects.
In this embodiment, as in preceding embodiments, the handle 28 can comprise a reusable component, and the carrier 104 and electrodes 106 can comprise a single use component that is temporarily fastened to the handle for use and then removed after use for disposal.
C. Dermal Temperature Sensing In all of the preceding embodiments, the controller 48 preferable relies upon sensing tissue temperature conditions as a form of active process feedback control.
For this purpose, the energy applicator carries at least one sensor 112 (see Fig. 12), which senses tissue temperature conditions. In the illustrated embodiment, the at least one sensor 112 is located beneath the epidermis 16 and into the dermis 18 (see Fig. 13), to sense actual tissue temperature conditions in the dermis 18.
When used in association with the applicator pad 66 of the category (i) applicator 3 0 ( 1 ) ( as Fig . 12 shows ) , an array .of probes 114 is arranged in a spaced-apart relationship along the periphery of the pad 66. Each probe 114 carries at least one temperature sensor 112. In use, the probes 114 extend through the epidermis 16 and into the dermis 18, as Fig. 13 shows.
When use in association with a penetrating needle electrode 82, 90, or 106, (see Fig. 14) each needle electrode 82, 90, or 106 can carry at least one temperature sensor 112. Alternatively, of course, probes could be used to carry the sensors 112, in the manner shown in Figs. 12 and 13. In any event, the sensors 112 are located so that, in use, they are positioned in the region of the dermis 118 where radio frequency heating is targeted, as Fig.
14 shows.
In the embodiment shown in Fig. 15, a tissue penetrating probe 116 (or needle electrode, as the case may be) may support a vertically stacked array 118 of temperature sensors 120. The temperature sensors 120 are arranged at known, fixed intervals along the probe 116. The stacked sensors 120 sense a dermal tissue temperature gradient along the length of the probe 116.
The sensing of a temperature gradient within dermal tissue targeted for radio frequency heating permits the controller 48 to identify along the gradient the location of the maximum tissue temperature region TMAX. For control purposes, the controller 48 can include an algorithm that selects the maximum tissue temperature TMAX and also identifies the depth D(TMAX) at which the maximum tissue temperature occurs. By varying the power of radio frequency energy applied and the rate of surface cooling (when appropriate), the controller 48 can adjust the maximum tissue temperature TMAX to achieve the desired control point temperature, which for collagen shrinkage is 65Q C. The controller 48 can also establish and maintain a control depth (D(TMAX) at which the desired control point temperature occurs, e.g., at a skin depth of 200 ~m to 300 ~cm (pre-set or set by the physician), to achieve optimal collagen shrinkage.
Various features of the invention are set forth in the following claims.
Fig. 6 is an exploded perspective view of another category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy internally directly into the dermis;
Fig. 7 is a side section view of the energy applicator shown in Fig. 6 in use to heat collagen tissue in the dermis;
Fig. 8 is an exploded perspective view, with portions in section, of another category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy into the dermis internally through subcutaneous tissue;
Fig. 9 is a side section view of the energy applicator shown in Fig. 8 in use to heat collagen tissue in the dermis;
Fig. 10 is an exploded, perspective view of another category of an energy applicator, usable in association with the system shown in Fig. 2, to transmit energy into the dermis from the backside of a surgically created facelift flap.
Fig. 11 is a side section view of the energy applicator shown in Fig. 10 in use to heat collagen tissue in the dermis from the backside of a facelift flap;
Fig. 12 is a perspective view of an energy applicator of the type shown in Fig. 3, with associated probes for sensing temperature in the dermis;
Fig. 13 is a side section view of an energy applicator shown in Fig. 3, with the sensors deployed in the dermis to sense temperature conditions;
Fig. 14 is a side section view of an energy applicator of the type shown in Fig. 6, with associated sensors located in the dermis to sense temperature conditions; and Fig. 15 is a side section view of a penetration tissue temperature sensing probe of the type shown in Figs. 12 to 14, with multiple sensors deployed in a stacked arrangement to sense a temperature gradient in the dermis.
The invention may be embodied in several forms without departing from its spirit or essential characteristics. The scope of the invention is defined in the appended claims, rather than in the specific description preceding them. All embodi-ments that fall within the meaning and range of equivalency of the claims are therefore intended to be embraced by the claims.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
The invention provides systems and methods of treating cosmetic conditions affecting the skin.
The system and methods are applicable for use throughout the body. However, the systems and methods are particularly well suited for treating cosmetic conditions in the facial or neck area of the body. For this reason, the systems and methods will be described in this context.
I. Anatomy of the Skin As Fig. 1 shows, the skin 10 overlies and protects subcutaneous tissue 12 and muscle tissue 14 of the body. In the face and neck areas, the skin 10 measures about 2mm in cross section.
The skin 10 includes an external, non-_ 7 _ vascular covering of epithelial cells, called the epidermis 16. In the face and neck regions, the epidermis measures about 100 ~,m in cross section.
The skin 10 also includes a layer of vascular tissue, named the dermis 18. In the face and neck regions, the dermis 18 measures about 1900 ~cm in cross section.
The dermis 18 is tough, flexible, and highly elastic. It is divided into a papillary (upper) layer 20 and a reticular (lower) layer 22.
The most numerous fibers in the papillary and reticular layers 20 and 22 are collagen fibers, which in large part account for the strength and physical properties of the dermis 18. Hair bulbs, sweat ducts, and other glands also occupy the reticular layer 22.
The f fibrous structure of collagen tissue is observed to dissociate and contract along its length when heated to a defined temperature condition, i.e., about 65 ~C. The contraction of collagen tissue causes the dermis 18 to reduce in size, which has an observable tightening effect. As collagen contacts, wrinkles and sag lines in the skin are ameliorated. As a result, the outward cosmetic appearance of the skin 10 improves.
The temperature conditions conducive to the beneficial results of collagen shrinkage lay well above the temperature conditions at which irreversible thermal damage to epithelial cells begins to occur, i.e., above about 47~ C.
II. systems for Renovating the Dermis A. System overview Fig. 2 shows a system 24 for renovating and reconstituting the dermis. The system 24 applies energy to the dermis to elevate and maintain its _ g _ temperature at a predetermined temperature condition, at or about 65Q C, without increasing the temperature of the epidermis beyond 47Q C. In this way, the system applies energy to the dermis in a targeted, selective fashion, to dissociate and contract collagen tissue, while preserving and protecting epithelial cells against thermal damage.
The system 24 includes a treatment device 26. The device 26 includes a handle 28 made, e.g., from molded plastic. The handle 28 carries at its distal end a treatment energy applicator 30, which, in use, contacts the epidermis. The handle 28 is sized to be conveniently grasped like a pencil or paint brush by a physician, to thereby manipulate the applicator 30 on the epidermis 16.
The system 24 further includes a device 32 to generate treatment energy. In the illustrated embodiment, the generator 32 generates radio frequency energy, e.g., having a frequency in the range of about 400 kHz to about 10 mHz.
A cable 34 extending from the proximal end of the handle 28 terminates with an electrical connector 36. The cable 34 is electrically coupled to the applicator 30, e.g., by wires that extend through the interior of the handle 28. When connector 36 plugs into the generator 32, to convey the generated energy to the applicator 30 for transmission to the skin.
The system 24 also includes certain auxiliary processing equipment 38 and 40. In the illustrated embodiment, the processing equipment 38 comprises an external fluid delivery apparatus, and the processing equipment 40 comprises an external aspirating apparatus.
The handle 28 of the treatment device 26 g includes one or more interior lumens 42. The lumens terminate in fittings 44 and 46, located at the proximal end of the handle 28. One fitting 44 connects to the fluid delivery apparatus 38, to convey processing fluid to the distal end of the handle 28 for discharge. The other fitting 46 connects to the aspirating apparatus 40, to convey aspirated material from the distal end of the handle 28 for discharge.
The system 24 also includes a controller 48. The controller 48, which preferably includes a central processing unit (CPU), is linked to the generator 32, the fluid delivery apparatus 38, and the aspirating apparatus 40. The controller 48 governs the power levels, cycles, and duration that the radio frequency energy is distributed to the applicator 30, to achieve and maintain power levels appropriate to achieve the desired treatment objectives. In tandem, the controller 48 also governs the delivery of processing fluid to the applicator 30 and the removal of aspirated material from the applicator 30.
The controller 48 includes an input/output (I/O) device 50.. The I/0 device 50 allows the physician to input control and processing variables, to enable the controller 48 to generate appropriate command signals. The I/O device 50 also receives real time processing feedback information from one or more sensors 52 associated with the applicator, for processing by the controller 48, e.g., to govern the application of energy and the delivery of processing fluid. The I/O device 50 also includes a display 54, to graphically present processing information to the physician for viewing or analysis.
H. The Treatment Device The ,structure of the treatment device 26 and associated electrical energy applicator 30 can vary.
The illustrated embodiments describe and show four representative categories of energy applicators 30, as follows:
(i) a first category applicator 30(1) (shown in Figs. 3 and 4) transmits energy into the dermis externally through the epidermis.
(ii) a second category applicator 30(2) (shown in Figs. 6 and 7) transmits energy internally directly into the dermis.
(iii) a third category applicator 30(3)(shown in Figs. 8 and 9) transmits energy into the dermis internally through subcutaneous tissue.
(iv) a fourth category applicator 30(4)(shown in Figs. 1o and 11) transmits energy into the dermis from the backside of a surgically created facelift flap.
The various categories of energy applicators 30(1), 30(2), 30(3), and 30(4) will now be discussed in greater detail.
(i). Epidermal Energy Applicator In this category, as shown in Fig. 3, the energy applicator 30(1) includes a carrier grid 56, which is mounted on the distal end of the handle 28.
The carrier grid 56 is made from an electrically non-conducting material, e.g., plastic or ceramic.
The carrier grid 56 carries a pattern of multiple, spaced apart electrodes 58. Each electrode 58 comprises a discrete transmission source of radio frequency energy. The electrodes 58 can be made, e.g., from stainless steel, platinum, and other noble metals, or combinations thereof. The electrodes 58 may be fastened to the grid by various means, e.g., by adhesives, by painting, or by other coating or deposition techniques.
In the illustrated embodiment, the carrier grid 56 is formed by an outside frame 60 with crossing interior spacers 62. Together, the frame 60 and spacers 62 define an open lattice of cells 64.
In the illustrated embodiment, the grid 56 defines sixteen cells 64. It should be appreciated that the cells 64 could number more or less than sixteen.
In the illustrated embodiment, the electrodes 58 are located on the grid 56 at the four corners of each cell 64. This arrangement provides a symmetric pattern of twenty-five electrodes 58 on the grid 56. Still, it should be appreciated that the electrodes 58 could be arranged in other symmetric or non-symmetric patterns in the grid.
In the embodiment shown in Fig. 3, the energy applicator 30(1) includes an external pad 66, which is attached peripherally about the carrier grid 56. The pad 66 is made from a resilient microporous membrane. As Fig. 4 shows, the pad 66, in use, makes surface contact with the epidermis 16.
The resilience of the pad 66 makes it well suited to conform to a variable surface topography of the epidermis 16.
The attachment of the pad about the carrier grid 56 creates an interior chamber 68, which encloses the grid 56. The applicator 30(1) further includes a fluid manifold 70 inside the chamber 68.
The fluid manifold 70 communicates with the fluid delivery apparatus 38, via the handle lumens 42.
The manifold 70 uniformly introduces processing fluid through the grid 56 and into the interior chamber 68.
In this arrangement, the processing fluid comprises an electrically conductive liquid, such as saline (about 0.9% to 3.0%). The apparatus 38 includes a pump 72 to convey the electrically conductive liquid through the manifold 70 at a prescribed rate.
The flow of the electrically conductive liquid into the through the grid 56 and into interior chamber 68 contacts the interior surface of the microporous membrane of the pad 66. As Fig. 4 shows, the microporous membrane of the pad 66 has pores 74 sized to permit passage of the electrically conductive fluid in the chamber 68 through the membrane and into contact with the epidermis 16 the membrane contacts.
The diffusion. of electrically conductive liquid through the membrane pores 74 serves two purposes. First, it creates conductive cooling at the interface between the membrane pad 66 and the epidermis 16. Second, it serves to ionically transport radio frequency energy transmitted by the grid electrodes 58 through the membrane pores 74, for return (in a unipolar arrangement) through exterior patch electrode 76 coupled to patient ground.
The ionically conducted radio frequency energy transported through the membrane pore 74 will, in turn, cause localized ohmic heating of skin tissue. The application of radio frequency energy by ionic transport to the epidermis surface, simultaneously combined with the conductive surface cooling effects that the ionic transport also provides, places the tissue region where maximum temperature conditions exist (designated TMAX in Fig. 4) at a location below the epidermis 16, into the papillary dermis 20 and, preferably, into the reticular dermis 22 as well.
The applicator 30(1) thereby makes possible selective heating of the interior dermis 18 to a maximum tissue temperature TMAX of about 65QC, while maintaining the temperature of the epidermis 16 at or about 20QC to 30QC, thereby avoiding thermal damage to the epidermis 16.
Alternatively, an electrically conductive jelly can occupy the interior chamber 68. The jelly causes ionic transport of radio frequency energy through the membrane pores 74. In this arrangement, a manifold 78 distributes fluid about the periphery of the pad 66, but not into the chamber 68 itself, to nevertheless cause connective surface cooling effects. In this arrangement, the fluid distributed by the manifold 78 need not be electrically conductive, but it can be to provide uniform distribution of the radio frequency energy at the pad 66.
In use, the physician places the pad 66 upon a targeted region of tissue. The controller 48 governs the application of radio frequency energy to the electrodes 58 in concert with the delivery of fluid to the manifold 70 (or 78), to control the desired epidermal and dermal tissue temperature conditions. The controller 48 can also govern the withdrawal of fluid from the vicinity of the pad 66 through the aspirating apparatus 40 for this purpose. The controller 48 can alter the distribution of the radio frequency energy among selected sets or subsets of one or more grid electrodes 58. In this way, the controller 48 can focus the application of radio frequency in selected patterns.
In maintaining control of the process, the controller 48 can depend upon empirically determined or modeled relationships among selected processing variables, including, e.g., tissue temperature, time, power, and fluid delivery rate, without actual temperature sensing. Preferably, however, localized tissue temperature conditions are sensed to provide direct feedback control, as will be described in greater detail later.
In the illustrated embodiment, the handle 28 and grid 56 can comprise reusable components. In this arrangement, the energy applicator pad 66 can comprise a single use component that is temporarily fastened to the handle 28 at time of use, e.g., by a conventional snap-fit, and then removed after use for disposal.
The pad 66 need not be sized to cover a targeted facial or neck region in its entirety.
Instead, the physician can locate the pad 66 in contact with a localized area of epidermal tissue within a targeted region. After applying the desired amount of radio frequency energy, the physician can relocate the pad 66 to an adjacent tissue area in the targeted region and again apply radio frequency energy. The physician can repeat this successive process, until the entire targeted region has been subject to treatment by exposure to radio frequency energy.
The energy applicator pads 66 can be specially shaped and contoured to provide different geometries, selected to match the topography of the targeted facial or neck region, e.g., under the eye (as pad 66(1) in Fig. 5 shows); or below the ear (as pad 66 ( 2 ) in Fig . 5 shows ) ; or under the chin ( as pad 66(3) in Fig. 5 shows); or around the lips (as pad 66(4) in Fig. 5 shows); or on the forehead above the eyebrows (as pad 66(5) in Fig. 5 shows).
(ii). Intradermal Energy Applicator As shown in Fig. 6, the second category of energy applicator 30(2) includes a carrier 80 on the distal end of the handle 28. The carrier 80 supports an array of spaced-apart needle electrodes 82. The electrodes 82 are metallic, being made, e.g., from stainless steel, platinum, other noble metals, or combinations thereof. Each electrode 82 comprises a discrete transmission source of radio frequency energy, which the controller 48 governs.
The carrier 80 can provide physical connections between control wires and each electrode 82, e.g., by solder or adhesive. Alternatively, the carrier 80 can have painted, coated, or otherwise deposited solid state circuitry to provide the electrical paths. The solid state circuitry can include a fuse element that interrupts electrical contact after a specified period of use, to thereby discourage reuse of the carrier 80.
In use (as Fig. 7 shows), the electrodes 82 are intended to be inserted as a unit on the carrier 80 through the epidermis 16 and into the dermis 18.
After insertion, the controller 48 conditions the electrodes 82 for operation in a unipolar mode. In this mode, energy transmitted by one or more of the electrodes 82 is returned by an indifferent patch electrode 84, which is coupled to patient ground.
Alternatively, the controller 48 can condition pairs of electrodes 82 to operate in a bipolar mode, with one electrode serving to transmit radio frequency energy, and the other electrode serving as the return path.
WO 00/48644 PCT/iJS00/02778 The size and spacing of the electrodes 82 shown in Figs. 10 and 11 are purposely set to penetrate the skin to a depth sufficient to pass entirely through the epidermis 16 and penetrate the papillary and, preferable, extend into the reticular dermis (e.g., about 200 ~m to 300 Vim). When used for this purpose, the electrodes 82 each possesses a total length of about 0.5 to about 3.0 mm. The electrodes are mutually spaced apart by about 0.5 mm to 10.0 mm.
An electrical insulating material 86 surrounds the proximal end of each electrode 82 by at least 0.5 mm. This leaves an exposed, non-insulated length at the distal end of about 0.5 mm to 2.5 mm. The insulating material 82 insulates the epidermis 16 and a portion of the dermis 18 from direct exposure to radio frequency energy transmitted by the exposed distal end.
The ratio between exposed and insulated regions on the electrodes 82 affects the impedance of the electrodes 82 during use. Generally speaking, the larger the exposed region is compared to the insulated region, a larger impedance value can be expected.
In use, the physician places the carrier 80 upon a desired region of tissue. The physician applies light pressure on the handle 28 to insert the needle electrodes 82 through the epidermis 16 and into the dermis 18. The controller 48 governs the application of radio frequency energy to the electrodes 82 to ohmically heat adjacent dermal tissue. The electrodes 82 can be operated individually or in groups to form defined energy application patterns. As before described, the controller 48 can depend upon the empirically determined or modeled relationships among processing variables to affect process control, with or without actual temperature sensing.
In this arrangement, the handle 28 can comprise a reusable component, and the carrier 80 with electrodes 82 can comprise a single use component, which is temporarily fastened to the distal end of the handle 28 for use and then removed after use for disposal.
As with the pad 66, the carrier 80 need not be sized to cover a targeted facial or neck region in its entirety. Instead, the physician can successive locate the carrier 80 in a localized areas within a targeted region, and apply radio frequency energy to each localized area.
Like the pad 66, the carrier 80 can also be specially shaped and contoured to provide different geometries, selected to match the topography of the targeted facial or neck region, as shown in Fig. 5.
(iii) Subdermal Energy Applicator As shown in Fig. 8, the third category of energy applicator 30(3) includes a carrier 88 mounted on the distal end of the handle 28. Like the carrier 80 shown in Fig. 6, the carrier 88 shown in Fig. 8 holds an array of spaced-apart, metallic needle electrodes 90. Each electrode 90 comprises a discrete transmission source of radio frequency energy, which the controller 48 governs.
As before explained, the carrier 88 can provide physical connections between control wires and each electrode 90, or carry painted, coated, or otherwise deposited solid state circuitry to provide the electrical paths.
As Fig. 9 best shows, the needle electrodes 90 shown in Fig. 8 differ from the electrode 82 in Fig. 6 in that they are longer than the needle electrodes 82. The longer electrodes 90 are intended to be inserted as a unit through both the epidermis 16 and the dermis 18, and extend into the subcutaneous tissue region 12 a short distance beyond the reticular dermis 22.
For this purpose, the electrodes 90 each possesses a total length of about 3.0 mm to 10.0 mm.
The electrodes 90 are mutually spaced apart by about 0.5 mm to 3.0 mm. An electrical insulating material 92 surrounds the proximal end of each electrode 90 by at least 2.0 mm. This leaves an exposed, non-insulated length at the distal end of each electrode 90 of about 3.0 mm to 4.0 mm. The insulating material 92 insulates the epidermis 16 and dermis 18 from direct exposure to radio frequency energy transmitted by the exposed distal ends of the electrodes 90.
In the illustrated embodiment, at least some, and preferably all, of the needle electrodes 90 include interior fluid passages 94 (see Fig. 8).
A manifold 96 couples a select number of the passages 94 in communication with the fluid delivery apparatus 38. This way, processing fluid can be introduced through the electrodes 90 and into the subcutaneous tissue surrounding the distal ends of the electrodes 90. The manifold 96 couples other passages 94 in communication with the aspirating device 40, to evacuate material through the distal ends of the electrodes 90.
In this embodiment, the processing fluid comprises an electrically conductive liquid, such as saline. The apparatus 38 includes a pump 72 (see Fig. 1) to convey the electrically conductive liquid to the manifold 96 at a prescribed rate. The manifold 96 disperses the electrically conductive liquid through the selected passages 94.
The controller conditions the electrodes 90 to operate in a unipolar mode. Energy transmitted by one or more of the electrodes 90 is returned by an indifferent patch electrode 100, which is coupled to patient ground (see Fig. 9). At the same time, electrically conductive liquid flows through the selected passages 94 into the surrounding subcutaneous tissue region 12 (shown by arrows 122 in Fig. 9), while liquid and other material is evacuated through the other passages 94 by the aspirating device 40 (as shown by arrows 124 in Fig.
9) .
The radio frequency energy transmitted by the exposed, distal ends of the electrodes 90 will cause localized ohmic heating of subcutaneous tissue. The conduction of the electrically conductive fluid ionically distributes the radio frequency energy in a uniform manner, while also providing a localized cooling effect. The cooling effect places the tissue region where maximum temperature conditions exist at a location (designated TMAX in Fig. 9) spaced from the distal ends of the electrodes 90, which includes the reticular dermis 22.
The localized heating effects will all cause fat tissue 102 in the subcutaneous tissue 12 to flow (see Fig. 9). Suction applied by the aspirating device 40 through the passages 94 can be used to evacuate flowing fat tissue from subcutaneous tissue 12 (as arrows 124 in Fig. 9 show). This provides localized liposuction effects in the subcutaneous region 12, in tandem with collagen heating effects in the dermis 18.
In use, the physician places the carrier 88 upon a desired region of tissue. The physician applies light pressure on the handle 18 to insert the needle electrodes 90 through the epidermis 16 and dermis 18 and into a subcutaneous tissue region 12. The controller 48 governs the application of radio frequency energy to the electrodes 90, which can be operated individually or in deffined patterns.
The carrier 88 need not be sized to cover an entire targeted region. The physician can locate the carrier 88 in successive local areas within a targeted region, and apply radio frequency energy to each localized area. Like the pad 66, the carrier 88 can also be specially shaped and contoured to provide different geometries, selected to match the topography of the targeted facial or neck region, as shown in Fig. 5.
As before described, the controller 48 can depend upon the empirically determined or modeled relationships among processing variables to affect process control, with or without actual temperature sensing.
In this embodiment, as in the preceding embodiment, the handle 28 can comprise a reusable component, and the carrier 88 and needle electrodes 90 can comprise a single use component that is temporarily fastened to the handle 28 for use and then removed after use for disposal.
(iv) Facelift Flap Energy Applicator As shown in Fig. 10, the fourth category of energy applicator 30(4) likewise includes a carrier 104 on the distal end of the handle 28. The carrier 104 holds a pair of bipolar metallic electrodes 106.
In use, energy transmitted by one of the electrodes - 21 °
106 is returned by the other electrode 106 to patient ground. Alternatively, the carrier 104 can hold an array of several needle electrodes, which are operated in either a bipolar or unipolar mode.
In use (see Fig. 11), the physician surgically creates a facelift flap 108 in the targeted tissue region. The flap 108 extends well into the dermis 18 (e.g., 200 ,gym to 300 Vim). The physician inserts the needle electrodes 106 into the backside of the flap 108 and applies radio frequency energy.
The size and spacing of the electrodes 106 are purposely set to penetrate into the backside of the skin flap 108 to a depth sufficient to locate the distal ends of the electrodes 106 in dermal tissue.
When used for this purpose, the electrodes 106 each possesses a total length of about 3.0 mm to 8.0 mm. The electrodes 106 are mutually spaced apart by about 0.5 mm to 10.0 mm.
Alternatively, in this embodiment, the applicator 30(4) can comprise an array of surface electrodes 106 that do not penetrate the skin flap 108, but which rest on the surface of the backside of the skin flap.
As before described, the controller 48 governs application of radio frequency energy to achieve the desired tissue effects.
In this embodiment, as in preceding embodiments, the handle 28 can comprise a reusable component, and the carrier 104 and electrodes 106 can comprise a single use component that is temporarily fastened to the handle for use and then removed after use for disposal.
C. Dermal Temperature Sensing In all of the preceding embodiments, the controller 48 preferable relies upon sensing tissue temperature conditions as a form of active process feedback control.
For this purpose, the energy applicator carries at least one sensor 112 (see Fig. 12), which senses tissue temperature conditions. In the illustrated embodiment, the at least one sensor 112 is located beneath the epidermis 16 and into the dermis 18 (see Fig. 13), to sense actual tissue temperature conditions in the dermis 18.
When used in association with the applicator pad 66 of the category (i) applicator 3 0 ( 1 ) ( as Fig . 12 shows ) , an array .of probes 114 is arranged in a spaced-apart relationship along the periphery of the pad 66. Each probe 114 carries at least one temperature sensor 112. In use, the probes 114 extend through the epidermis 16 and into the dermis 18, as Fig. 13 shows.
When use in association with a penetrating needle electrode 82, 90, or 106, (see Fig. 14) each needle electrode 82, 90, or 106 can carry at least one temperature sensor 112. Alternatively, of course, probes could be used to carry the sensors 112, in the manner shown in Figs. 12 and 13. In any event, the sensors 112 are located so that, in use, they are positioned in the region of the dermis 118 where radio frequency heating is targeted, as Fig.
14 shows.
In the embodiment shown in Fig. 15, a tissue penetrating probe 116 (or needle electrode, as the case may be) may support a vertically stacked array 118 of temperature sensors 120. The temperature sensors 120 are arranged at known, fixed intervals along the probe 116. The stacked sensors 120 sense a dermal tissue temperature gradient along the length of the probe 116.
The sensing of a temperature gradient within dermal tissue targeted for radio frequency heating permits the controller 48 to identify along the gradient the location of the maximum tissue temperature region TMAX. For control purposes, the controller 48 can include an algorithm that selects the maximum tissue temperature TMAX and also identifies the depth D(TMAX) at which the maximum tissue temperature occurs. By varying the power of radio frequency energy applied and the rate of surface cooling (when appropriate), the controller 48 can adjust the maximum tissue temperature TMAX to achieve the desired control point temperature, which for collagen shrinkage is 65Q C. The controller 48 can also establish and maintain a control depth (D(TMAX) at which the desired control point temperature occurs, e.g., at a skin depth of 200 ~m to 300 ~cm (pre-set or set by the physician), to achieve optimal collagen shrinkage.
Various features of the invention are set forth in the following claims.
Claims (43)
1. A device for applying electromagnetic energy to skin comprising a carrier, an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, and a microporous pad on the carrier overlying the array of electrodes forming an interior chamber to contain an electrically conductive material, the microporous pad adapted, in use, to contact an epidermal skin region and ionically transport the applied electromagnetic energy to ohmically heat dermal tissue beneath the epidermal skin region.
2. A device according to claim 1 wherein the carrier is shaped to match a targeted skin region topography.
3. A device according to claim 1 wherein the microporous pad is made from a resilient material to conform to a variable epidermal skin region topography.
4. A device according to claim 1 wherein the electrically conductive material comprises an electrically conductive liquid.
5. A device according to claim 1 wherein the electrically conductive material comprises an electrically conductive jelly.
6. A device according to claim 5 further including a manifold on the carrier to distribute liquid about the microporous pad.
7. A device according to claim 1 further including at least one temperature sensing probe on the carrier.
8. A device according to claim 7 wherein the temperature sensing probe is located outside the microporous pad .
9. A device according to claim 7 wherein the temperature sensing probe is sized to extend into dermal tissue when the microporous pad contacts the epidermal tissue region.
10. A device according to claim 7 wherein the temperature sensing probe carries more than one temperature sensor.
11. A device according to claim 1 wherein the array of electrodes is arranged to create a pattern for applying the electromagnetic energy.
12. A family of devices for applying electromagnetic energy to skin, each device comprising a carrier having a shape, an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, and a microporous pad on the carrier overlying the array of electrodes forming an interior chamber to contain an electrically conductive material, the microporous pad adapted, in use, to contact an epidermal skin region and ionically transport the applied electromagnetic energy to ohmically heat dermal tissue beneath the epidermal skin region, and the shape of the carriers differing to match different skin region topographies.
13. A method for applying electromagnetic energy to skin comprising the steps of providing a carrier, an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, and a microporous pad on the carrier overlying the array of electrodes forming an interior chamber to contain an electrically conductive material, and placing the microporous pad in contact with an epidermal skin region while applying the electromagnetic energy with the electrodes to ionically transport the applied electromagnetic energy through the microporous pad to ohmically heat dermal tissue beneath the epidermal skin region.
14. A method according to claim 13 further including the step of circulating the electrically conductive material in the interior chamber while applying the electromagnetic energy.
15. A method according to claim 13 further including the step of distributing liquid about the microporous pad while applying the electromagnetic energy.
16. A method according to claim 13 further including the step of sensing temperature while applying the electromagnetic energy.
17. A method according to claim 16 wherein the temperature sensing step includes sensing temperature of dermal tissue beneath the epidermal tissue region.
18. A device for applying electromagnetic energy to skin comprising a carrier, and an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, the electrodes being sized so that, while the carrier contacts an epidermal skin region, the electrodes extend into tissue beneath the epidermal skin region to ohmically heat dermal tissue.
19. A device according to claim 18 wherein the electrodes are sized to extend into dermal tissue.
20. A device according to claim 18 wherein the electrodes are sized to extend into subdermal tissue.
21. A device according to claim 18 wherein each electrode has a distal end, and further including an electrical insulating material on at least some of the electrodes while leaving the respective distal end free of the electrical insulating material.
22. A device according to claim 18 wherein at least some of the electrodes include an interior passage for conveying fluid.
23. A device according to claim 18 wherein the carrier is shaped to match a topography of the epidermal skin region.
24. A device according to claim 18 further including at least one temperature sensing probe on the carrier.
25. A device according to claim 24 wherein the temperature sensing probe is sized to extend into tissue beneath the epidermal tissue region.
26. A device according to claim 18 further including a temperature sensor carried by at least one of the electrodes.
27. A device according to claim 18 further including more than one temperature sensor carried by at least one of the electrodes.
28. A device according to claim 18 wherein the array of electrodes is arranged to create a pattern for applying the electromagnetic energy.
29. A family of devices for applying electromagnetic energy to skin, each device comprising a carrier having a shape, an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, the electrodes being sized so that, while the carrier contacts an epidermal skin region, the electrodes extend into tissue beneath the epidermal skin region to ohmically heat dermal tissue, and the shape of the carriers differing to match different skin region topographies.
30. A method for applying electromagnetic energy to skin comprising the steps of providing a carrier, an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, the electrodes being sized so that, while the carrier contacts an epidermal skin region, the electrodes extend into tissue beneath the epidermal skin region, and placing the carrier in contact with an epidermal skin region while applying the electromagnetic energy with the electrodes to ohmically heat tissue beneath the epidermal skin region.
31. A method according to claim 30 further including the step of conveying a liquid through an interior passage in at least some of the electrodes while applying the electromagnetic energy.
32. A method according to claim 30 further including the step of sensing temperature while applying the electromagnetic energy.
33. A method according to claim 32 wherein the temperature sensing step includes sensing temperature of dermal tissue beneath the epidermal tissue region.
34. A method according to claim 30 wherein the electrodes ohmically heat dermal tissue.
35. A method according to claim 30 wherein the electrodes ohmically heat dermal and subdermal tissue.
36. A device for applying electromagnetic energy to a facelift flap comprising a carrier, and at least one electrode on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, the electrode being sized so that, while the carrier contacts a backside of the flap, the electrode ohmically heat the dermal tissue.
37. A device according to claim 36 wherein the electrode, in use, rests on a surface on the backside of the flap.
38. A device according to claim 36 wherein the electrode is sized to, in use, extend into dermal tissue within the flap.
39. A family of devices for applying electromagnetic energy to skin, each device comprising a carrier having a shape, an array of electrodes on the carrier connectable to a source of electromagnetic energy to apply the electromagnetic energy, and the shape of the carriers differing to match different skin region topographies.
40. A family according to claim 39 wherein the carrier is adapted, in use, to contact epidermal tissue, and wherein the electrodes are sized to extend into tissue beneath the epidermal tissue.
41. A family according to claim 39 wherein the electrodes are sized to extend into dermal tissue.
42. A family according to claim 39 wherein the electrodes are sized to extend into subdermal tissue.
43. A family according to claim 39 further including a pad overlying the electrodes that, in use, contacts epidermal tissue.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US09/251,554 US6277116B1 (en) | 1994-05-06 | 1999-02-17 | Systems and methods for shrinking collagen in the dermis |
| US09/251,554 | 1999-02-17 | ||
| PCT/US2000/002778 WO2000048644A2 (en) | 1999-02-17 | 2000-02-02 | Systems and methods for shrinking collagen in the dermis |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2362276A1 true CA2362276A1 (en) | 2000-08-24 |
Family
ID=22952463
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002362276A Abandoned CA2362276A1 (en) | 1999-02-17 | 2000-02-02 | Systems and methods for shrinking collagen in the dermis |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US6277116B1 (en) |
| EP (1) | EP1152701A2 (en) |
| AU (1) | AU757624B2 (en) |
| CA (1) | CA2362276A1 (en) |
| WO (1) | WO2000048644A2 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US10575897B2 (en) | 2004-04-01 | 2020-03-03 | The General Hospital Corporation | Method and apparatus for dermatological treatment and tissue reshaping |
Families Citing this family (207)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6024733A (en) * | 1995-06-07 | 2000-02-15 | Arthrocare Corporation | System and method for epidermal tissue ablation |
| US6425912B1 (en) * | 1995-05-05 | 2002-07-30 | Thermage, Inc. | Method and apparatus for modifying skin surface and soft tissue structure |
| US7758537B1 (en) | 1995-11-22 | 2010-07-20 | Arthrocare Corporation | Systems and methods for electrosurgical removal of the stratum corneum |
| US20030212393A1 (en) * | 1996-01-05 | 2003-11-13 | Knowlton Edward W. | Handpiece with RF electrode and non-volatile memory |
| US7229436B2 (en) | 1996-01-05 | 2007-06-12 | Thermage, Inc. | Method and kit for treatment of tissue |
| US6091995A (en) * | 1996-11-08 | 2000-07-18 | Surx, Inc. | Devices, methods, and systems for shrinking tissues |
| US6104959A (en) | 1997-07-31 | 2000-08-15 | Microwave Medical Corp. | Method and apparatus for treating subcutaneous histological features |
| US7494488B2 (en) * | 1998-05-28 | 2009-02-24 | Pearl Technology Holdings, Llc | Facial tissue strengthening and tightening device and methods |
| US6391023B1 (en) | 1998-05-28 | 2002-05-21 | Pearl Technology Holdings, Llc | Thermal radiation facelift device |
| US6678556B1 (en) * | 1998-07-13 | 2004-01-13 | Genetronics, Inc. | Electrical field therapy with reduced histopathological change in muscle |
| EP2428250A1 (en) * | 1998-07-13 | 2012-03-14 | Genetronics, Inc. | Skin and muscle-targeted gene therapy by pulsed electrical field |
| US7922709B2 (en) | 1998-07-13 | 2011-04-12 | Genetronics, Inc. | Enhanced delivery of naked DNA to skin by non-invasive in vivo electroporation |
| ES2240078T3 (en) * | 1999-03-09 | 2005-10-16 | Thermage, Inc. | APPARATUS FOR TREATMENT OF FABRICS. |
| US6587730B2 (en) * | 1999-07-27 | 2003-07-01 | Mattioli Engineering Ltd. | Method and apparatus for skin brown spot removal and collagen formation |
| US20020087155A1 (en) * | 1999-08-30 | 2002-07-04 | Underwood Ronald A. | Systems and methods for intradermal collagen stimulation |
| AU2594801A (en) * | 1999-12-30 | 2001-07-16 | Pearl Technology Holdings, Llc | Face-lifting device |
| US20080033492A1 (en) * | 2000-01-07 | 2008-02-07 | Biowave Corporation | Electro-therapy method |
| US20070016268A1 (en) * | 2000-01-07 | 2007-01-18 | John Carter | Percutaneous electrode array |
| US20040092860A1 (en) * | 2000-07-26 | 2004-05-13 | Dev Nagendu B. | Skin and muscle-targeted gene therapy by pulsed electrical field |
| US20040006379A1 (en) * | 2000-10-06 | 2004-01-08 | Expanding Concepts, L.L.C. | Epidural thermal posterior annuloplasty |
| US6673063B2 (en) * | 2000-10-06 | 2004-01-06 | Expanding Concepts, Llc. | Epidural thermal posterior annuloplasty |
| US6740085B2 (en) * | 2000-11-16 | 2004-05-25 | Olympus Corporation | Heating treatment system |
| US20040162551A1 (en) * | 2000-12-15 | 2004-08-19 | Brown Tony R. | Method and device for creating transmural lesions |
| US7422586B2 (en) * | 2001-02-28 | 2008-09-09 | Angiodynamics, Inc. | Tissue surface treatment apparatus and method |
| US7464781B2 (en) * | 2002-02-22 | 2008-12-16 | Bombardier Recreational Product Inc. | Three-wheeled vehicle having a split radiator and an interior storage compartment |
| US6662054B2 (en) * | 2002-03-26 | 2003-12-09 | Syneron Medical Ltd. | Method and system for treating skin |
| US8986297B2 (en) * | 2002-08-21 | 2015-03-24 | Resect Medical, Inc. | Thermal hemostasis and/or coagulation of tissue |
| US7341586B2 (en) * | 2002-08-21 | 2008-03-11 | Resect Medical, Inc. | Thermal coagulation of tissue during tissue resection |
| EP1613202B1 (en) * | 2003-03-27 | 2011-02-09 | The General Hospital Corporation | Apparatus for dermatological treatment and fractional skin resurfacing |
| GB0322766D0 (en) * | 2003-09-29 | 2003-10-29 | Emcision Ltd | Surgical resection device |
| US7613523B2 (en) * | 2003-12-11 | 2009-11-03 | Apsara Medical Corporation | Aesthetic thermal sculpting of skin |
| GB0402569D0 (en) * | 2004-02-05 | 2004-03-10 | Neurodan As | Nerve and/or muscle stimulation electrodes |
| US20080082090A1 (en) * | 2004-04-01 | 2008-04-03 | The General Hospital Corporation | Method and apparatus for dermatological treatment and tissue reshaping |
| US7331953B2 (en) * | 2004-04-01 | 2008-02-19 | The Gneral Hospital Corporation | Method and apparatus for dermatological treatment |
| EP3695799A1 (en) * | 2004-04-05 | 2020-08-19 | The General Hospital Corporation | Device and method for treating tissue |
| US8571648B2 (en) * | 2004-05-07 | 2013-10-29 | Aesthera | Apparatus and method to apply substances to tissue |
| US7842029B2 (en) * | 2004-05-07 | 2010-11-30 | Aesthera | Apparatus and method having a cooling material and reduced pressure to treat biological external tissue |
| US20060047281A1 (en) * | 2004-09-01 | 2006-03-02 | Syneron Medical Ltd. | Method and system for invasive skin treatment |
| JP4950055B2 (en) * | 2004-10-19 | 2012-06-13 | メーガン メディカル インコーポレイティッド | Methods and means for electrical stimulation of cutaneous sensory receptors |
| US8417352B2 (en) * | 2004-10-19 | 2013-04-09 | Meagan Medical, Inc. | System and method for stimulating sensory nerves |
| US20120226271A1 (en) * | 2005-03-25 | 2012-09-06 | Peter Callas | Vacuum Ablation Apparatus and Method |
| US7713266B2 (en) | 2005-05-20 | 2010-05-11 | Myoscience, Inc. | Subdermal cryogenic remodeling of muscles, nerves, connective tissue, and/or adipose tissue (fat) |
| US7850683B2 (en) * | 2005-05-20 | 2010-12-14 | Myoscience, Inc. | Subdermal cryogenic remodeling of muscles, nerves, connective tissue, and/or adipose tissue (fat) |
| US8024022B2 (en) * | 2005-05-25 | 2011-09-20 | Alfred E. Mann Foundation For Scientific Research | Hermetically sealed three-dimensional electrode array |
| US20060287615A1 (en) * | 2005-06-15 | 2006-12-21 | Tsung-I Yu | Massaging mask |
| WO2007019365A2 (en) * | 2005-08-03 | 2007-02-15 | Massachusetts Eye & Ear Infirmary | Targeted muscle ablation for reducing signs of aging |
| US7967763B2 (en) * | 2005-09-07 | 2011-06-28 | Cabochon Aesthetics, Inc. | Method for treating subcutaneous tissues |
| US8518069B2 (en) | 2005-09-07 | 2013-08-27 | Cabochon Aesthetics, Inc. | Dissection handpiece and method for reducing the appearance of cellulite |
| JP2009506873A (en) * | 2005-09-07 | 2009-02-19 | ザ ファウンドリー， インコーポレイテッド | Apparatus and method for disrupting subcutaneous structures |
| US10548659B2 (en) | 2006-01-17 | 2020-02-04 | Ulthera, Inc. | High pressure pre-burst for improved fluid delivery |
| US9486274B2 (en) | 2005-09-07 | 2016-11-08 | Ulthera, Inc. | Dissection handpiece and method for reducing the appearance of cellulite |
| US9011473B2 (en) | 2005-09-07 | 2015-04-21 | Ulthera, Inc. | Dissection handpiece and method for reducing the appearance of cellulite |
| US9358033B2 (en) * | 2005-09-07 | 2016-06-07 | Ulthera, Inc. | Fluid-jet dissection system and method for reducing the appearance of cellulite |
| US7957815B2 (en) | 2005-10-11 | 2011-06-07 | Thermage, Inc. | Electrode assembly and handpiece with adjustable system impedance, and methods of operating an energy-based medical system to treat tissue |
| US8702691B2 (en) | 2005-10-19 | 2014-04-22 | Thermage, Inc. | Treatment apparatus and methods for delivering energy at multiple selectable depths in tissue |
| US20070142885A1 (en) * | 2005-11-29 | 2007-06-21 | Reliant Technologies, Inc. | Method and Apparatus for Micro-Needle Array Electrode Treatment of Tissue |
| US9248317B2 (en) | 2005-12-02 | 2016-02-02 | Ulthera, Inc. | Devices and methods for selectively lysing cells |
| US7885793B2 (en) | 2007-05-22 | 2011-02-08 | International Business Machines Corporation | Method and system for developing a conceptual model to facilitate generating a business-aligned information technology solution |
| US20080195036A1 (en) * | 2005-12-02 | 2008-08-14 | Cabochon Aesthetics, Inc. | Devices and methods for selectively lysing cells |
| US7920926B2 (en) * | 2005-12-09 | 2011-04-05 | Apsara Medical Corporation | Method and apparatus for carrying out the controlled heating of tissue in the region of dermis |
| US8048089B2 (en) | 2005-12-30 | 2011-11-01 | Edge Systems Corporation | Apparatus and methods for treating the skin |
| US8961511B2 (en) * | 2006-02-07 | 2015-02-24 | Viveve, Inc. | Vaginal remodeling device and methods |
| US20070213705A1 (en) * | 2006-03-08 | 2007-09-13 | Schmid Peter M | Insulated needle and system |
| ITRM20060166A1 (en) * | 2006-03-24 | 2007-09-25 | Promoitalia Internat Srl | SUBDERMAL PROBE FOR AESTHETIC RADIOFREQUENCY TREATMENTS |
| US9566088B2 (en) | 2006-03-29 | 2017-02-14 | Edge Systems Llc | Devices, systems and methods for treating the skin |
| US20070244529A1 (en) * | 2006-04-18 | 2007-10-18 | Zoom Therapeutics, Inc. | Apparatus and methods for treatment of nasal tissue |
| EP2018129B1 (en) | 2006-05-12 | 2020-04-01 | Vytronus, Inc. | Device for ablating body tissue |
| EP2034917A2 (en) * | 2006-07-05 | 2009-03-18 | Bovie Medical | Apparatus and method for skin tightening and corrective forming |
| US20080027520A1 (en) * | 2006-07-25 | 2008-01-31 | Zoom Therapeutics, Inc. | Laser treatment of tissue |
| US20080027423A1 (en) * | 2006-07-25 | 2008-01-31 | Zoom Therapeutics, Inc. | Systems for treatment of nasal tissue |
| US8007493B2 (en) * | 2006-10-16 | 2011-08-30 | Syneron Medical Ltd. | Methods and devices for treating tissue |
| US8273080B2 (en) | 2006-10-16 | 2012-09-25 | Syneron Medical Ltd. | Methods and devices for treating tissue |
| US8133216B2 (en) | 2006-10-16 | 2012-03-13 | Syneron Medical Ltd. | Methods and devices for treating tissue |
| US8142426B2 (en) * | 2006-10-16 | 2012-03-27 | Syneron Medical Ltd. | Methods and devices for treating tissue |
| US20080097557A1 (en) * | 2006-10-19 | 2008-04-24 | Apsara Medical Corporation | Method and apparatus for carrying out the controlled heating of tissue in the region of dermis |
| US9254162B2 (en) | 2006-12-21 | 2016-02-09 | Myoscience, Inc. | Dermal and transdermal cryogenic microprobe systems |
| WO2008091983A2 (en) * | 2007-01-25 | 2008-07-31 | Thermage, Inc. | Treatment apparatus and methods for inducing microburn patterns in tissue |
| US8211099B2 (en) * | 2007-01-31 | 2012-07-03 | Tyco Healthcare Group Lp | Thermal feedback systems and methods of using the same |
| US8409185B2 (en) | 2007-02-16 | 2013-04-02 | Myoscience, Inc. | Replaceable and/or easily removable needle systems for dermal and transdermal cryogenic remodeling |
| US9149331B2 (en) | 2007-04-19 | 2015-10-06 | Miramar Labs, Inc. | Methods and apparatus for reducing sweat production |
| WO2008131306A1 (en) | 2007-04-19 | 2008-10-30 | The Foundry, Inc. | Systems and methods for creating an effect using microwave energy to specified tissue |
| US20100114086A1 (en) | 2007-04-19 | 2010-05-06 | Deem Mark E | Methods, devices, and systems for non-invasive delivery of microwave therapy |
| RU2523620C2 (en) | 2007-04-19 | 2014-07-20 | Мирамар Лэбс,Инк. | Systems and methods for generating exposure on target tissue with using microwave energy |
| US20080269735A1 (en) * | 2007-04-26 | 2008-10-30 | Agustina Vila Echague | Optical array for treating biological tissue |
| US9364287B2 (en) * | 2007-06-05 | 2016-06-14 | Reliant Technologies, Inc. | Method for reducing pain of dermatological treatments |
| US20080312648A1 (en) * | 2007-06-12 | 2008-12-18 | Darion Peterson | Fat removal and sculpting device |
| US8845630B2 (en) | 2007-06-15 | 2014-09-30 | Syneron Medical Ltd | Devices and methods for percutaneous energy delivery |
| US20120143178A9 (en) * | 2007-06-15 | 2012-06-07 | Primaeva Medical, Inc. | Devices and methods for percutaneous energy delivery |
| US20090012434A1 (en) * | 2007-07-03 | 2009-01-08 | Anderson Robert S | Apparatus, method, and system to treat a volume of skin |
| WO2009009661A1 (en) | 2007-07-10 | 2009-01-15 | Thermage, Inc. | Treatment apparatus and methods for delivering high frequency energy across large tissue areas |
| US8103355B2 (en) * | 2007-07-16 | 2012-01-24 | Invasix Ltd | Method and device for minimally invasive skin and fat treatment |
| US20090069795A1 (en) * | 2007-09-10 | 2009-03-12 | Anderson Robert S | Apparatus and method for selective treatment of tissue |
| US8430920B2 (en) * | 2007-09-28 | 2013-04-30 | Kasey K. LI | Device and methods for treatment of tissue |
| US20090093723A1 (en) * | 2007-10-05 | 2009-04-09 | Cabochon Aesthetics, Inc. | Ultrasound device including dispenser |
| US20090093864A1 (en) * | 2007-10-08 | 2009-04-09 | Anderson Robert S | Methods and devices for applying energy to tissue |
| EP2209424A1 (en) * | 2007-10-09 | 2010-07-28 | Cabochon Aesthetics, Inc. | Ultrasound apparatus with treatment lens |
| US8439940B2 (en) | 2010-12-22 | 2013-05-14 | Cabochon Aesthetics, Inc. | Dissection handpiece with aspiration means for reducing the appearance of cellulite |
| US20090093738A1 (en) * | 2007-10-09 | 2009-04-09 | Cabochon Aesthetics, Inc. | Device and method for monitoring a treatment area |
| US20090157152A1 (en) * | 2007-10-19 | 2009-06-18 | Shiseido Company, Ltd. | Cosmetic method for improving skin condition of face and neck, and apparatus thereof |
| WO2009059186A1 (en) | 2007-10-31 | 2009-05-07 | Primaeva Medical, Inc. | Cartridge electrode device |
| US20090112205A1 (en) * | 2007-10-31 | 2009-04-30 | Primaeva Medical, Inc. | Cartridge electrode device |
| US8298216B2 (en) * | 2007-11-14 | 2012-10-30 | Myoscience, Inc. | Pain management using cryogenic remodeling |
| EP2394594A1 (en) * | 2007-12-05 | 2011-12-14 | Syneron Medical Ltd. | A disposable electromagnetic energy applicator and method of using it |
| BRPI0820706B8 (en) | 2007-12-12 | 2021-06-22 | Miramar Labs Inc | disposable medical device for use with an applicator |
| US20090156958A1 (en) | 2007-12-12 | 2009-06-18 | Mehta Bankim H | Devices and methods for percutaneous energy delivery |
| EP2231274B1 (en) | 2007-12-12 | 2014-03-12 | Miramar Labs, Inc. | System and apparatus for the noninvasive treatment of tissue using microwave energy |
| JP5508285B2 (en) | 2008-01-04 | 2014-05-28 | エッジ システムズ コーポレーション | Apparatus and method for treating skin |
| WO2009090632A2 (en) | 2008-01-17 | 2009-07-23 | Syneron Medical Ltd. | A hair removal apparatus for personal use and the method of using same |
| CN101951851B (en) | 2008-01-24 | 2013-02-06 | 赛诺龙医疗公司 | A device and apparatus of adipose tissue treatment |
| WO2009099988A2 (en) * | 2008-02-01 | 2009-08-13 | The General Hospital Corporation | Method and apparatus for fat removal |
| KR100852500B1 (en) * | 2008-03-31 | 2008-08-18 | (주)엠큐어 | Gun type multi injection microneedle theraphy system |
| JP5181791B2 (en) * | 2008-04-03 | 2013-04-10 | ソニー株式会社 | Voltage controlled variable frequency oscillation circuit and signal processing circuit |
| US8682426B2 (en) * | 2008-04-07 | 2014-03-25 | Old Dominion Research Foundation | Delivery device, system, and method for delivering nanosecond pulsed electric fields |
| EP2271276A4 (en) | 2008-04-17 | 2013-01-23 | Miramar Labs Inc | Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy |
| US20090312693A1 (en) * | 2008-06-13 | 2009-12-17 | Vytronus, Inc. | System and method for delivering energy to tissue |
| US9155588B2 (en) | 2008-06-13 | 2015-10-13 | Vytronus, Inc. | System and method for positioning an elongate member with respect to an anatomical structure |
| CA2726934C (en) * | 2008-06-14 | 2018-04-24 | Vytronus, Inc. | System and method for delivering energy to tissue |
| US8882753B2 (en) * | 2008-07-14 | 2014-11-11 | Syneron Medical Ltd | Devices and methods for percutaneous energy delivery |
| WO2010009150A1 (en) | 2008-07-14 | 2010-01-21 | Primaeva Medical, Inc. | Devices and methods for percutaneous energy delivery |
| US20100017750A1 (en) | 2008-07-16 | 2010-01-21 | Avner Rosenberg | User interface |
| US9314293B2 (en) | 2008-07-16 | 2016-04-19 | Syneron Medical Ltd | RF electrode for aesthetic and body shaping devices and method of using same |
| US20100049099A1 (en) * | 2008-07-18 | 2010-02-25 | Vytronus, Inc. | Method and system for positioning an energy source |
| US10363057B2 (en) | 2008-07-18 | 2019-07-30 | Vytronus, Inc. | System and method for delivering energy to tissue |
| KR101013581B1 (en) * | 2008-08-06 | 2011-02-14 | 라종주 | Electric Skin Treatment Device |
| KR102124591B1 (en) * | 2008-08-07 | 2020-06-19 | 더 제너럴 하스피탈 코포레이션 | Skin treatment device for dermatological hypopigmentation |
| EP2163218A1 (en) * | 2008-09-16 | 2010-03-17 | Osyris Medical | Device for treating part of a human or animal body comprising an instrument for dispensing and/or an instrument for locally sucking up treatment doses and means for controlling dosimetry |
| EP2334249B1 (en) | 2008-09-21 | 2013-03-13 | Syneron Medical Ltd. | A method and apparatus for personal skin treatment |
| US20100106063A1 (en) * | 2008-10-29 | 2010-04-29 | Cabochon Aesthetics, Inc. | Ultrasound Enhancing Target for Treating Subcutaneous Tissue |
| US9033885B2 (en) * | 2008-10-30 | 2015-05-19 | Vytronus, Inc. | System and method for energy delivery to tissue while monitoring position, lesion depth, and wall motion |
| US11298568B2 (en) | 2008-10-30 | 2022-04-12 | Auris Health, Inc. | System and method for energy delivery to tissue while monitoring position, lesion depth, and wall motion |
| US8414508B2 (en) | 2008-10-30 | 2013-04-09 | Vytronus, Inc. | System and method for delivery of energy to tissue while compensating for collateral tissue |
| US9192789B2 (en) | 2008-10-30 | 2015-11-24 | Vytronus, Inc. | System and method for anatomical mapping of tissue and planning ablation paths therein |
| US9220924B2 (en) | 2008-10-30 | 2015-12-29 | Vytronus, Inc. | System and method for energy delivery to tissue while monitoring position, lesion depth, and wall motion |
| CA2742787C (en) | 2008-11-17 | 2018-05-15 | Vytronus, Inc. | Systems and methods for ablating body tissue |
| US8475379B2 (en) * | 2008-11-17 | 2013-07-02 | Vytronus, Inc. | Systems and methods for ablating body tissue |
| US8357150B2 (en) | 2009-07-20 | 2013-01-22 | Syneron Medical Ltd. | Method and apparatus for fractional skin treatment |
| KR20110119640A (en) | 2008-12-22 | 2011-11-02 | 마이오우사이언스, 인크. | Integrated cryosurgical system with refrigerant and electrical power source |
| US8882758B2 (en) * | 2009-01-09 | 2014-11-11 | Solta Medical, Inc. | Tissue treatment apparatus and systems with pain mitigation and methods for mitigating pain during tissue treatments |
| US8506506B2 (en) | 2009-01-12 | 2013-08-13 | Solta Medical, Inc. | Tissue treatment apparatus with functional mechanical stimulation and methods for reducing pain during tissue treatments |
| KR100943089B1 (en) * | 2009-01-23 | 2010-02-18 | 강동환 | Handpiece for treating skin |
| US9254168B2 (en) * | 2009-02-02 | 2016-02-09 | Medtronic Advanced Energy Llc | Electro-thermotherapy of tissue using penetrating microelectrode array |
| US20100211055A1 (en) * | 2009-02-18 | 2010-08-19 | Shimon Eckhouse | Method for body toning and an integrated data management system for the same |
| EP2730313A1 (en) | 2009-02-25 | 2014-05-14 | Syneron Medical Ltd. | Electrical skin rejuvenation |
| KR20120090007A (en) | 2009-02-25 | 2012-08-16 | 프리마바 메디컬, 아이엔씨. | Devices and methods for percutaneous energy delivery |
| US8167280B2 (en) * | 2009-03-23 | 2012-05-01 | Cabochon Aesthetics, Inc. | Bubble generator having disposable bubble cartridges |
| US20100249772A1 (en) * | 2009-03-26 | 2010-09-30 | Primaeva Medical, Inc. | Treatment of skin deformation |
| US20100256596A1 (en) * | 2009-04-07 | 2010-10-07 | Cabochon Aesthetics, Inc. | Fiber growth promoting implants for reducing the appearance of cellulite |
| EP2440150A4 (en) * | 2009-06-09 | 2012-11-14 | Gen Hospital Corp | Method and apparatus for dermatological treatment and tissue reshaping |
| US8788060B2 (en) * | 2009-07-16 | 2014-07-22 | Solta Medical, Inc. | Tissue treatment systems with high powered functional electrical stimulation and methods for reducing pain during tissue treatments |
| RU2012107673A (en) * | 2009-08-04 | 2013-09-10 | Поллоген Лтд. | COSMETIC REJUVENATION OF SKIN |
| US9358064B2 (en) | 2009-08-07 | 2016-06-07 | Ulthera, Inc. | Handpiece and methods for performing subcutaneous surgery |
| US11096708B2 (en) | 2009-08-07 | 2021-08-24 | Ulthera, Inc. | Devices and methods for performing subcutaneous surgery |
| CN105879238B (en) | 2009-09-18 | 2019-10-18 | 女康乐公司 | Repair the instrument and method of vagina tissue |
| US8361069B2 (en) * | 2009-09-25 | 2013-01-29 | Covidien Lp | Energized needles for wound sealing |
| US11590346B2 (en) | 2009-11-16 | 2023-02-28 | Pollogen Ltd. | Apparatus and method for cosmetic treatment of human mucosal tissue |
| KR20120116934A (en) | 2009-11-16 | 2012-10-23 | 폴로젠 리미티드 | Non-invasive fat removal |
| US20110202048A1 (en) * | 2010-02-12 | 2011-08-18 | Solta Medical, Inc. | Methods for pain reduction with functional thermal stimulation and tissue treatment systems |
| US11565107B2 (en) * | 2010-03-01 | 2023-01-31 | Inovio Pharmaceuticals, Inc. | Tolerable and minimally invasive skin electroporation device |
| US20120158100A1 (en) | 2010-06-21 | 2012-06-21 | Kevin Schomacker | Driving Microneedle Arrays into Skin and Delivering RF Energy |
| US8968289B2 (en) | 2010-10-22 | 2015-03-03 | Covidien Lp | Microwave spacers and methods of use |
| JP6040159B2 (en) * | 2010-12-03 | 2016-12-07 | シネロン メディカル リミテッド | Device to improve electrode skin contact |
| KR20140088044A (en) | 2010-12-13 | 2014-07-09 | 마이오우사이언스, 인크. | Method for reducing hyperdynamic facial wrinkles |
| CN102631243B (en) * | 2011-02-15 | 2014-09-17 | 成功大学 | Therapeutic device for electromagnetic thermotherapy |
| US9409006B2 (en) * | 2011-04-10 | 2016-08-09 | David Hirshberg | Fat removal device and obesity treatment |
| US20120271219A1 (en) * | 2011-04-19 | 2012-10-25 | David John Weisgerber | Combined Energy and Topical Composition Application For Regulating the Condition of Mammalian Skin |
| US20120270743A1 (en) * | 2011-04-19 | 2012-10-25 | David John Weisgerber | Genetic Signatures and Gene Chips Associated With Administration of Electrically Conducted Radio Frequency Current to Skin and Methods and Treatments Relating Thereto |
| KR101277450B1 (en) * | 2011-04-21 | 2013-06-27 | 주식회사 루트로닉 | A treatment apparutus using radio frequency energy |
| JP5908977B2 (en) * | 2011-06-14 | 2016-04-26 | ジョンジュ ナ | Apparatus and method for improving skin with Lar effect or Laplacian effect |
| DK3473296T3 (en) | 2011-06-28 | 2020-11-09 | Inovio Pharmaceuticals Inc | MINIMALLY INVASIVE DERMAL ELECTROPORATION UNIT |
| US9314301B2 (en) | 2011-08-01 | 2016-04-19 | Miramar Labs, Inc. | Applicator and tissue interface module for dermatological device |
| ES2562990T3 (en) * | 2011-09-05 | 2016-03-09 | Venus Concept Ltd | Improved aesthetic device to beautify the skin |
| WO2013076714A1 (en) * | 2011-11-24 | 2013-05-30 | Synerom Medical Ltd | A safe skin treatment apparatus for personal use and method for its use |
| BR112014017175A8 (en) | 2012-01-13 | 2017-07-04 | Myoscience Inc | skin protection for subdermal cryogenic remodeling for cosmetic and other treatments |
| CA2861116A1 (en) | 2012-01-13 | 2013-07-18 | Myoscience, Inc. | Cryogenic probe filtration system |
| US9314290B2 (en) | 2012-01-13 | 2016-04-19 | Myoscience, Inc. | Cryogenic needle with freeze zone regulation |
| US9017318B2 (en) | 2012-01-20 | 2015-04-28 | Myoscience, Inc. | Cryogenic probe system and method |
| US9277958B2 (en) | 2012-02-22 | 2016-03-08 | Candela Corporation | Reduction of RF electrode edge effect |
| US9889297B2 (en) | 2012-02-22 | 2018-02-13 | Candela Corporation | Reduction of RF electrode edge effect |
| CN103301567B (en) | 2012-03-16 | 2016-04-06 | 女康乐公司 | A kind of therapeutic apparatus repairing vagina tissue |
| DE102012010262B4 (en) | 2012-05-25 | 2014-07-03 | Albrecht Molsberger | Therapeutically applicable DC delivery device |
| US20140088670A1 (en) * | 2012-09-25 | 2014-03-27 | Ines Verner Rashkovsky | Devices and methods for stimulation of hair growth |
| US20140188128A1 (en) | 2012-12-31 | 2014-07-03 | Paul Joseph Weber | Systems, apparatus and methods for tissue dissection and modification |
| US10045761B2 (en) | 2012-12-31 | 2018-08-14 | Tdm Surgitech, Inc. | Systems, apparatus and methods for tissue dissection |
| DE102013000966A1 (en) * | 2013-01-22 | 2014-07-24 | Zimmer Medizinsysteme Gmbh | Method and apparatus for continuous non-invasive measurement of tissue temperatures at different tissue depths |
| US9962546B2 (en) | 2013-02-21 | 2018-05-08 | Meagan Medical, Inc. | Cutaneous field stimulation with disposable and rechargeable components |
| EP2967633B1 (en) | 2013-03-15 | 2018-04-25 | Edge Systems LLC | Devices for treating the skin |
| US9610112B2 (en) | 2013-03-15 | 2017-04-04 | Myoscience, Inc. | Cryogenic enhancement of joint function, alleviation of joint stiffness and/or alleviation of pain associated with osteoarthritis |
| US9295512B2 (en) | 2013-03-15 | 2016-03-29 | Myoscience, Inc. | Methods and devices for pain management |
| WO2014146127A1 (en) | 2013-03-15 | 2014-09-18 | Myoscience, Inc. | Methods and systems for treatment of spasticity |
| US20140350536A1 (en) | 2013-03-15 | 2014-11-27 | Myoscience, Inc. | Cryogenic Blunt Dissection Methods and Devices |
| US9827140B2 (en) | 2013-07-17 | 2017-11-28 | William Thomas McClellan | Percutaneous blepharoplasty device and method |
| WO2015013502A2 (en) | 2013-07-24 | 2015-01-29 | Miramar Labs, Inc. | Apparatus and methods for the treatment of tissue using microwave energy |
| US20150342661A1 (en) * | 2013-10-09 | 2015-12-03 | Venus Concept Ltd | Integrated Treatment System |
| US10130409B2 (en) | 2013-11-05 | 2018-11-20 | Myoscience, Inc. | Secure cryosurgical treatment system |
| WO2016103245A1 (en) * | 2014-07-24 | 2016-06-30 | Sasi Solomon | Device and methods for delivery of stimulation to a body tissue |
| US10179229B2 (en) | 2014-12-23 | 2019-01-15 | Edge Systems Llc | Devices and methods for treating the skin using a porous member |
| EP4324414A2 (en) | 2014-12-23 | 2024-02-21 | HydraFacial LLC | Devices and methods for treating the skin using a rollerball or a wicking member |
| EP3454762B1 (en) | 2016-05-13 | 2024-04-03 | Pacira CryoTech, Inc. | Systems for locating and treating with cold therapy |
| US11511110B2 (en) | 2018-06-27 | 2022-11-29 | Viveve, Inc. | Methods for treating urinary stress incontinence |
| US11896823B2 (en) | 2017-04-04 | 2024-02-13 | Btl Healthcare Technologies A.S. | Method and device for pelvic floor tissue treatment |
| EP3651674A4 (en) * | 2017-08-29 | 2021-07-21 | Patchmi, Inc. | Microneedle treatment system |
| WO2019099677A1 (en) | 2017-11-15 | 2019-05-23 | Myoscience, Inc. | Integrated cold therapy and electrical stimulation systems for locating and treating nerves and associated methods |
| EP3870090B1 (en) | 2018-10-23 | 2023-09-27 | Aesthetics Biomedical, Inc. | Systems for inducing collagen regeneration |
| FR3122826A1 (en) | 2021-05-12 | 2022-11-18 | L'oreal | METHODS AND COMPOSITIONS FOR IMPROVING SKIN |
| FR3124952A1 (en) | 2021-07-09 | 2023-01-13 | L'oreal | Methods and compositions for improving the skin |
| US11779389B2 (en) | 2021-08-27 | 2023-10-10 | Ilooda Co., Ltd. | Skin treatment device |
| USD1016615S1 (en) | 2021-09-10 | 2024-03-05 | Hydrafacial Llc | Container for a skin treatment device |
Family Cites Families (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4448198A (en) * | 1979-06-19 | 1984-05-15 | Bsd Medical Corporation | Invasive hyperthermia apparatus and method |
| US6068653A (en) * | 1992-11-13 | 2000-05-30 | Scimed Life Systems, Inc. | Electrophysiology catheter device |
| US5374283A (en) * | 1993-12-01 | 1994-12-20 | Flick; A. Bart | Electrical therapeutic apparatus |
| DE4414807C2 (en) * | 1994-04-28 | 1996-10-02 | Willmen Hans Rainer | Electrosurgical instrument for the therapy of varices |
| US5458596A (en) * | 1994-05-06 | 1995-10-17 | Dorsal Orthopedic Corporation | Method and apparatus for controlled contraction of soft tissue |
| US5681308A (en) * | 1994-06-24 | 1997-10-28 | Stuart D. Edwards | Ablation apparatus for cardiac chambers |
| US5588960A (en) * | 1994-12-01 | 1996-12-31 | Vidamed, Inc. | Transurethral needle delivery device with cystoscope and method for treatment of urinary incontinence |
| US6430446B1 (en) * | 1995-05-05 | 2002-08-06 | Thermage, Inc. | Apparatus for tissue remodeling |
| US5660836A (en) * | 1995-05-05 | 1997-08-26 | Knowlton; Edward W. | Method and apparatus for controlled contraction of collagen tissue |
| US6077257A (en) * | 1996-05-06 | 2000-06-20 | Vidacare, Inc. | Ablation of rectal and other internal body structures |
| US6081749A (en) * | 1997-08-13 | 2000-06-27 | Surx, Inc. | Noninvasive devices, methods, and systems for shrinking of tissues |
| US5916213A (en) * | 1997-02-04 | 1999-06-29 | Medtronic, Inc. | Systems and methods for tissue mapping and ablation |
| US5919188A (en) * | 1997-02-04 | 1999-07-06 | Medtronic, Inc. | Linear ablation catheter |
| US5843078A (en) * | 1997-07-01 | 1998-12-01 | Sharkey; Hugh R. | Radio frequency device for resurfacing skin and method |
| US6010500A (en) * | 1997-07-21 | 2000-01-04 | Cardiac Pathways Corporation | Telescoping apparatus and method for linear lesion ablation |
| US6030384A (en) * | 1998-05-01 | 2000-02-29 | Nezhat; Camran | Bipolar surgical instruments having focused electrical fields |
-
1999
- 1999-02-17 US US09/251,554 patent/US6277116B1/en not_active Expired - Lifetime
-
2000
- 2000-02-02 EP EP00915739A patent/EP1152701A2/en not_active Withdrawn
- 2000-02-02 AU AU36964/00A patent/AU757624B2/en not_active Ceased
- 2000-02-02 WO PCT/US2000/002778 patent/WO2000048644A2/en active IP Right Grant
- 2000-02-02 CA CA002362276A patent/CA2362276A1/en not_active Abandoned
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US10575897B2 (en) | 2004-04-01 | 2020-03-03 | The General Hospital Corporation | Method and apparatus for dermatological treatment and tissue reshaping |
Also Published As
| Publication number | Publication date |
|---|---|
| WO2000048644A3 (en) | 2000-12-14 |
| WO2000048644A9 (en) | 2002-03-28 |
| AU757624B2 (en) | 2003-02-27 |
| WO2000048644A2 (en) | 2000-08-24 |
| AU3696400A (en) | 2000-09-04 |
| US6277116B1 (en) | 2001-08-21 |
| EP1152701A2 (en) | 2001-11-14 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US6277116B1 (en) | Systems and methods for shrinking collagen in the dermis | |
| US11833364B2 (en) | Tissue treatment apparatus and systems with pain mitigation and methods for mitigating pain during tissue treatments | |
| US20210275825A1 (en) | Rf device for skin and fat treatment | |
| EP2401026B1 (en) | Electrical skin rejuvenation | |
| US8788060B2 (en) | Tissue treatment systems with high powered functional electrical stimulation and methods for reducing pain during tissue treatments | |
| CA2244479C (en) | Apparatus and method for treatment of body tissues | |
| US9161802B2 (en) | Patterned electrodes for tissue treatment systems | |
| KR101464058B1 (en) | A disposable electromagnetic energy applicator and method of using it | |
| AU779100B2 (en) | Apparatus and method for treatment of tissue | |
| US6920883B2 (en) | Methods and apparatus for skin treatment | |
| US20110202048A1 (en) | Methods for pain reduction with functional thermal stimulation and tissue treatment systems | |
| US20110190726A1 (en) | Method and apparatus for micro-needle array electrode treatment of tissue | |
| WO2003086217A1 (en) | Method for treatment of tissue | |
| WO2005117736A2 (en) | Method and apparatus for shrinking tissue | |
| US20200360072A1 (en) | Microneedle treatment system | |
| US20160228177A1 (en) | A system for periodontal treatment | |
| CN110213999B (en) | Device and method for cold plasma skin resurfacing | |
| IL213561A (en) | Apparatus for electrical skin rejuvenation | |
| FR3128645A3 (en) | DEVICE AND METHOD FOR UNATTENDED TREATMENT OF THE PATIENT |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |