System and method for heating biological tissue via RF energy

A system 30 and method(s) 100 for thermal treatment of a selected target within a subject is disclosed. System 30 includes RF source 10, phase shifter 14, impedance matching network 11 and resonator 13. Applicator 3 conveys output signal 17 from energy source 10 through surface 6 of biological tissue 4 to predetermined energy dissipation zone 5 after output 17 has been processed by the phase shifter 14, IMN 11 and resonator 13. Stationary water molecules 1, such as those in fat cells, are heated. System 30 is operative to heat a volume of biological tissue beneath the biological tissue surface 6 such that surface 6 of biological tissue 4 is maintained at a lower temperature than predetermined energy dissipation zone 5 without a cooling device. The invention is useful in selective heating of cellulite bodies as a means of treating cellulite.

FIELD AND BACKGROUND OF THE INVENTION

The present invention relates to an improved system and method for heating biological tissue via RF energy and, more particularly, to a system and method which rely upon a single electrode. Control of phase and pulse width modulation of applied RF waves facilitate efficient heating of underlying layers of tissue such as dermis and subcutaneous layers. Specifically, heating and contraction of adipose tissues as a means of cellulite reduction is achieved.

Adipose tissues, particularly cellulite, are typically treatable only with a strict regimen of diet and exercise. Patient compliance with these previously available regimens is poor. Cellulite occurs when fat cells swell compressing the flow of blood and lymph. This leads to build-up of fluid and toxins. Connective tissue forms hard fibrous capsules around the fat cells. This results in a “lumpy” appearance. The fat cells involved are located primarily in the third and most deep (skin) layer, which has a variable by thickness depending on the amount fat in the subject. Thickness of this layer typically increases in areas such as abdomen, thighs and buttocks.

Previously proposed methods for cellulite treatment include Topical treatment, Teas and capsules, Cellulite wraps, Endermologie, Mesotherapy, Acthyderm and Ultrasonic and particularly focused ultrasonic treatment. These techniques have demonstrated various degrees of clinical efficacy in reducing the “lumpy” appearance associated with cellulite deposits.

In addition, thermotherapy using electromagnetic radiation or radio-frequency (RF) waves has been proposed. RF treatment is more effective than other available therapy regimens since it permits the body to heal itself. Non-invasive electromagnetic radiation, including radio-frequency waves, has been proposed in the prior art for treatment of fat and cellulite in addition to use for contraction of collagen, such as involved in the treatment of wrinkles.

The typical RF technique for heating of biological tissues involves exposing the tissue to RF voltage, which produces RF conductive current through the tissue at a level sufficient to overcome the tissue resistance. The current heats the tissue. This method causes uneven heat accompanied by burning of the outer layer(s) the skin. As a result, many of the conventional systems for implementation of this method share, as an inherent disadvantage, a strict requirement for a cooling mechanism to remove an excessive heat of the skin during the treatment.

One example of a prior art system(s) is disclosed in U.S. Pat. No. 6,662,054 assigned to Syneron Medical Ltd. This patent teaches deforming the skin so that a region of skin protrudes from the surrounding skin, and applying RF energy to the protruded skin. The system includes one or more RF electrodes, configured to apply conducted RF current to the skin, and a skin deformer, so that a region of skin protrudes out from surrounding skin and is exposed to the conducted RF current, which follows the deforming act. Teachings of this patent include a strict requirement for cooling of the skin to prevent burning.

US Patent Application No. 20040002705 assigned to Thermage, Inc. also discloses a system that requires cooling of skin to prevent burning. In particular, this published patent application teaches a method of creating a tissue effect by delivering electromagnetic energy through a skin surface from an electromagnetic energy delivery device coupled to an electromagnetic energy source.

Further additional examples of prior art systems which require cooling of the skin to prevent burning include those disclosed in US Patent Application No. 2004030332 and U.S. Pat. No. 5,919,219 assigned to Thermage, Inc., which teach a system and method for providing treatment to a skin surface by applying RF energy through the skin using a memory for gathering information. These systems include express requirements for a cooling lumen for receiving cooling fluid and a number of RF electrodes. The RF electrodes are provided to transfer RF current to the skin and are configured to be capacitive coupled to the skin surface, thus creating a heating effect through RF conducted current.

In summary, the above-described prior art-methods require the use of a separate cooling system to cool the outer skin layer throughout the RF treatment. Further, many of the previously available solutions require a memory unit to store local information pertaining to the treated area throughout the treatment. Further, many of the previously available solutions require extensive preliminary adjustments, such as local impedance matching, prior to each treatment. Further, despite use of the phrase “one or more electrodes in many prior art documents, the above-described alternatives share a strict requirement for a return electrode pad to be placed against the patient to receive the RF currents after passing tissue being treated. This return electrode for volumetric treatment of adipose tissue (e.g. cellulite) routes a majority of energy through blood and lymphatic vessels. Fat cells are heated only by heat dissipated from these non-target tissues as a result of their inherent resistance.

There is thus a widely recognized need for, and it would be highly advantageous to have, an improved system and method for heating biological tissue via RF energy that attempts to address one or more of the limitations of the above-described systems.

SUMMARY OF THE INVENTION

According to one aspect of the present invention there is provided a system for RF (HF) energy treatment of deep layers of human tissue (e.g.dermis and/or hypodermis) to achieve adipose tissue contraction and/or cellulite reduction.

The system includes an RF-energy applicator (e.g.spherical shape) which serves as RF-energy coupling antenna that functions in combination with an adjacent tissue as a losses transmission line when contacted with epidermis of the tissue.

The system further includes a treated area (part) of human tissue placed in direct contact with RF-energy applicator whereas underlying subcutaneous tissues acts as a dissipative load of the said applicator and the transmission line.

The system further includes a parallel resonance circuit (RF-resonator) including inductor and capacitor and maximally closely contacted with the said applicator by its central point whereas merit factor of this resonant circuit must be sufficiently high that provides active losses determined by equivalent resistance, which is at least 20 times higher that modulus of impedance of a said area of attached human tissue

The system further includes impedance matching network (IMN) converting the impedance of treated area of human tissue into 50 Ohms in order to minimize reflected power from human tissue and provide a traveling wave through a human tissue.

The system further includes a phase shifting device at the input of the IMN providing an achievement of maximum of RF traveling-wave at a predetermined depth under the surface or on the surface.

According to another aspect of the present invention there is provided a method, which includes operation of the system.

According to further features in preferred embodiments of the invention described below the applicator is made from Al, Ag, Au, copper, or copper and aluminum alloys and coated with dielectric material.

According to still further features in the described preferred embodiments the applicator is made from Al coated by alumina.

According to still further features in the described preferred embodiments the applicator is moved on the surface of treated skin.

According to still further features in the described preferred embodiments the feeding cable connects RF-applicator and RF-resonator with impedance matching systems.

According to still further features in the described preferred embodiments the feeding cable has resonance (n*λ/2) length, where λ is a wavelength of RF-energy in the cable material and n is whole number

According to still further features in the described preferred embodiments the impedance matching system provides compensation of the reactance of the attached piece of human tissue.

According to still further features in the described preferred embodiments the impedance matching system is fixed L, T or Π-shape structure.

According to still further features in the described preferred embodiments the impedance matching system is broadband impedance transformer.

According to still further features in the described preferred embodiments the impedance matching system is variable.

According to still further features in the described preferred embodiments the phase shifter is trombone type.

According to still further features in the described preferred embodiments the phase shifter is constructed of coaxial cable.

According to still further features in the described preferred embodiments the phase shift provided by the phase shifter is variable in time.

According to still further features in the described preferred embodiments the impedance meter (sensor) is inserted between matching system and RF-applicator.

According to still further features in the described preferred embodiments the said impedance matching system is controllable by feedback system obtaining the signal from the said impedance meter (sensor) for the purpose of reaching the optimal impedance matching and maximal energy deposition into human tissue.

According to still further features in the described preferred embodiments the coupled energy is delivered from RF-generator (amplifier).

According to still further features in the described preferred embodiments the delivered RF-power is coupled in continuous or pulsing mode.

According to still further features in the described preferred embodiments the control of the energy coupled to human tissue is achieved by variation of amplitude or. duty cycle of RF-power in pulsing mode (PWM-control).

According to still further features in the described preferred embodiments the certain part of human body is in contact with second point of the said RF-resonator (for example ground).

According to still further features in the described preferred embodiments the operation is provided on the resonance frequency of human body.

According to still further features in the described preferred embodiments the treatment with RF-applicator t is combined with the laser treatment.

According to still further features in the described preferred embodiments the treatment with RF-applicator t is combined with ultrasonic treatment

According to still further features in the described preferred embodiments the treatment with RF-applicator t is combined with UV-treatment

According to still further features in the described preferred embodiments the treatment with RF-applicator t is combined with plasma treatment

According to still further features in the described preferred embodiments the treatment with RF-applicator t is combined with flash-lamp treatment.

According to one aspect of the present invention there is provided an improved system for thermal treatment of a selected target within a subject, the system includes: (a) an RF energy source capable of producing an output RF power signal directed to an applicator contactable with a surface of a biological tissue belonging to the subject, the applicator capable of delivering a desired amount of energy to a predetermined energy dissipation zone beneath the surface of the biological tissue, the selected target positioned within the predetermined energy dissipation zone; (b) a phase shifter, the phase shifter capable of shifting a phase of directed traveling waves of the output signal so that energy therefrom is concentrated primarily in the predetermined energy dissipation zone, which lies at a desired depth beneath the surface of the biological tissue; (c) an impedance matching network (IMN), the IMN capable of converting the impedance of the biological tissue belonging to the subject from a nominal value to a corrected value, the corrected value matching an impedance characteristic of the RF transmission line so that the directed traveling wave may pass through the surface of the biological tissue without being converted to a standing wave; (d) an RF resonator located in the applicator, the RF resonator capable of cyclically accumulating and releasing the desired amount of energy, the RF resonator further capable of concentrating the desired amount of energy so that a significant portion thereof is concentrated in the predetermined energy dissipation zone; and (e) the applicator capable of conveying the output RF power signal from the RF energy source through the surface of the biological tissue to the predetermined energy dissipation zone after the output has been processed by the phase shifter, the IMN and the resonator. Operation of the system heats a volume of biological tissue beneath the biological tissue surface so that the surface of the biological tissue is maintained at a lower temperature that the predetermined energy dissipation zone5without requiring a cooling device. The absence of a ground electrode permits free propagation of the waves of the output RF power signal in the energy dissipation zone.

According to another aspect of the present invention there is provided an improved method for thermal treatment of a selected target within a subject. The method includes: (a) providing an output RF power signal directed to an applicator contactable with a surface of a biological tissue belonging to the subject, (b) employing a phase shifter to shift a phase of directed traveling waves of the output RF power so that energy therefrom is concentrated primarily in a predetermined energy dissipation zone which lies at a desired depth beneath the surface of the biological tissue, wherein the selected target is positioned within the predetermined energy dissipation zone; (c) converting the impedance of the biological tissue belonging to the subject from a nominal value to a corrected value, the corrected value matching an impedance characteristic of RF-transmission line so that the directed traveling wave may pass through the surface of the biological tissue without being converted to a standing wave by means of an impedance matching network (IMN); (d) cyclically accumulating in an RF resonator located in the applicator, and releasing therefrom, the desired amount of energy, (e) concentrating the desired amount of energy in the RF resonator so that a significant portion thereof is concentrated in the predetermined energy dissipation zone upon release therefrom; and (f) conveying the output signal of RF energy through the surface of the biological tissue to the predetermined energy dissipation zone after the output has been processed by the phase shifter, the IMN and the resonator by means of the applicator. Performance of (a)-(f) heats a volume of biological tissue beneath the biological tissue surface so that the surface of the biological tissue is maintained at a lower temperature than the predetermined energy dissipation zone5without requiring a cooling device. The absence of a ground electrode permits free propagation of the waves in the output signal in the energy dissipation zone.

According to yet another aspect of the present invention there is provided an improved method for cellulite treatment. The method includes: (a) providing an output signal of RF energy directable to an applicator contactable with a surface of a biological tissue belonging to the subject, (b) employing a phase shifter to shift a phase of directed traveling waves of the output RF power so that energy therefrom is concentrated primarily in a predetermined energy dissipation zone which lies at a desired depth beneath the surface of the biological tissue, wherein the selected target is positioned within the predetermined energy dissipation zone, the predetermined energy dissipation zone including at least one cellulite body; (c) converting the impedance of the biological tissue belonging to the subject from a nominal value to a corrected value, the corrected value matching an impedance characteristic of RF-transmission line so that the directed traveling wave so that the output signal may pass through the surface of the biological tissue without being converted to a standing wave by means of an impedance matching network (IMN); (d) cyclically accumulating in an RF resonator located in the applicator, and releasing therefrom, the desired amount of energy, (e) concentrating the desired amount of energy in the RF resonator so that a significant portion thereof is concentrated in the predetermined energy dissipation zone upon release therefrom; and (f) conveying the output power from the RF energy source through the surface of the biological tissue to the predetermined energy dissipation zone after the output has been processed by the phase shifter, the IMN and the resonator by means of the applicator. Performance of (a)-(f) heats a volume of biological tissue beneath the biological tissue surface so that the surface of the biological tissue is maintained at a lower temperature than the predetermined energy dissipation zone5without requiring a cooling device. The absence of a ground electrode permits free propagation of the waves in the output signal in the energy dissipation zone. The at least one cellulite body is heated to a greater degree than a tissue adjacent thereto.

According to further features in preferred embodiments of the invention described below, the system further includes a pulse width modulation (PWM)-controller, the PWM-controller capable of causing the RF energy source to deliver the output signal in pulses of a desired amplitude, a predetermined duration with a desired repetition frequency for average output power control.

According to still further features in the described preferred embodiments the system further includes a dielectric barrier positionable between the applicator and the surface of the biological tissue; the dielectric barrier preventing transmission of a conductive current.

According to still further features in the described preferred embodiments the applicator is made from at least one metal selected from the group consisting of aluminum, silver, gold, copper and alloys thereof.

According to still further features in the described preferred embodiments the dielectric barrier is supplied as a dielectric coating on the applicator.

According to still further features in the described preferred embodiments the applicator is constructed primarily of aluminum and the dielectric barrier is supplied as an alumina coating.

According to still further features in the described preferred embodiments the applicator is movable on the surface of the biological tissue as a means of altering a location of the energy dissipation zone.

According to still further features in the described preferred embodiments the system further includes a feeding cable, the feeding cable connecting the RF-applicator and the RF-resonator with the IMN.

According to still further features in the described preferred embodiments the feeding cable has a resonance length defined by n*λ/2 length, where λ is a wavelength of RF-energy in the cable material and n is a whole number.

According to still further features in the described preferred embodiments the IMN includes a fixed structure characterized by a shape selected from the group consisting of L shaped, T shaped and Π-shaped structure.

According to still further features in the described preferred embodiments the IMN includes a broadband impedance transformer.

According to still further features in the described preferred embodiments the IMN is variable.

According to still further features in the described preferred embodiments the phase shifter includes a trombone type phase shifting mechanism. Trombone type phase shifters are well known to those of ordinary skill in the art and are described in detail at www.microwaves101.com/encyclopedia/phaseshifters.cfm which is fully incorporated herein by reference (see Appendix A).

According to still further features in the described preferred embodiments the phase shifter is at least partially constructed of coaxial cable.

According to still further features in the described preferred embodiments a phase shift provided by the phase shifter is variable.

According to still further features in the described preferred embodiments the energy delivered to the predetermined energy dissipation zone is coupled in continuous or pulsing mode. The RF-energy is produced in the form of sinusoidal signal that can be modulated by rectangular pulses with lower frequency by PWM controller)

According to still further features in the described preferred embodiments the RF-energy is characterized by a resonance frequency which matches a known natural resonance frequency of the selected target

According to still further features in the described preferred embodiments the system further includes at least one additional component selected from the group consisting of a laser beam, an ultrasonic transducer, a UV light source, a plasma treatment device and a flash lamp.

According to still further features in the described preferred embodiments the providing indicates provision of the output signal in pulses of a predetermined duration with a desired frequency.

According to still further features in the described preferred embodiments the method further includes interposing a dielectric barrier between the applicator and the surface of the biological tissue. The dielectric barrier prevents transmission of a conductive current.

According to still further features in the described preferred embodiments the method further includes constructing the applicator primarily of aluminum. More preferably, the dielectric barrier is supplied as an alumina coating on an aluminum applicator.

According to still further features in the described preferred embodiments the method further includes moving the applicator with respect to the surface of the biological tissue as a means of altering a location of the energy dissipation zone.

According to still further features in the described preferred embodiments the method further includes employing a feeding cable to connect the RF-applicator and the RF-resonator with the IMN.

According to still further features in the described preferred embodiments the method further includes varying the phase shift provided by the phase shifter.

The present invention successfully addresses the shortcomings of the presently known configurations by providing an improved system and method for heating biological tissue via RF energy, which relies upon a single electrode and does not require a cooling system to prevent burning of skin.

BRIEF DESCRIPTION OF PREFERRED EMBODIMENTS

The present invention is of an improved system and method for heating biological tissue via RF energy, which requires only a single electrode. Specifically, control of phase and pulse with modulation (PWM)-control of applied RF waves through the single electrode of the present invention obviate the need for cooling of the skin surface while facilitating efficient heating of underlying layers of tissue such as dermis and subcutaneous layers. As a result, the desired heating and contraction of adipose tissues is achieved. This allows, for the first time, non-invasive cellulite reduction.

The principles and operation of an improved system and method for heating biological tissue via RF energy according to the present invention may be better understood with reference to the drawings and accompanying descriptions.

The present invention offers several advantages with regard to previously available alternatives.

A single electrode, or applicator, employed without a ground electrode permits homogeneous application of RF-energy, which is directed primarily towards rotation, and vibration of dipole molecules, especially water molecules, in the applied electromagnetic wave.

Phase shifting techniques provide the possibility of concentration of RF-energy at a predetermined location by variation of position of RF-wave maximum

Preferably, an Alumina-ceramic-coated applicator minimizes energy losses and prevents unwanted conductive current through human tissue

A supporting parallel resonator attached in proximity to the applicator accumulates RF-energy and provides efficient excitation of the applicator and high RF-voltage on the application surface.

Application of high RF-power in short-pulses provides fast and effective heating of cellulite capsules with relatively low average RF-power level.

PWM-control of output RF-power and simple IMN techniques provide good matching and low RF-power reflection with all types of human tissues. The additional advantage of applied fixed IMN and PWM-control ensure good impedance matching with variable types of human tissue without complicated impedance matching correction. The RF-applicator can be moved on the treated surface.

It will be appreciated that volumetric fatty tissue treatment requires deployment of a homogeneous RF-wave (through cross-section transversal to wave propagation) with maximum at a desired distance from the electrode-applicator. This homogeneous and high intensity RF-wave insures efficient heating of cellulite capsules and fat cells because they retain water molecules. In contrast, blood and lymphatic vessels will not be subject to undesired heating because the natural circulation of water molecules in these vessels provides convective cooling. Further, blood and lymphatic vessels provide conductive cooling for other non-target tissues such as muscle, nerve tissue and connective tissue.

Referring now to the figures, principle components of a system according to the present invention and their operation are explained in greater detail.

The present invention is primarily embodied by a system30(FIGS. 1-3) for thermal treatment of a selected target within a subject. System30includes an RF energy source10capable of producing an output RF power signal17directed to an applicator3contactable with a surface6of a biological tissue4belonging to the subject. Applicator3is capable of delivering a desired amount of energy to a predetermined energy dissipation zone5beneath surface6of biological tissue4. The selected target is positioned within the predetermined energy dissipation zone5and is represented in the figures as water molecules1.

System30further includes a phase shifter (e.g. trombone-type phase shifter14). Phase shifter14is capable of shifting a phase of directed traveling waves of output power17so that energy therefrom is concentrated primarily in the predetermined energy dissipation zone5, which lies at a desired depth beneath surface6of biological tissue4.

System30further includes an impedance matching network11(IMN capable of converting the impedance of biological tissue4belonging to the subject from a nominal value (e.g. 250-350 Ohms) to a corrected value (e.g. 50 Ohms). The corrected value matches an impedance characteristic of RF energy source and RF transmission line including phase shifter14and cable11, so that output RF traveling wave17may pass through surface6of biological tissue4without being converted to a standing wave.

System30further includes an RF resonator13located in applicator3., RF resonator13is capable of cyclically accumulating and releasing the desired amount of energy and is further capable of concentrating the desired amount of energy so that a significant portion thereof may be transmitted to predetermined energy dissipation zone5.

System30further includes applicator3capable of conveying output RF power signal17from the RF energy source10through surface6of biological tissue4to predetermined energy dissipation zone5after output17has been processed by the phase shifter14, IMN11and resonator13.

Typically, operation of system30results in 2 to 4% loss of energy from output signal17with ban additional 2-4% reflection of energy from output signal17. This means that system30can reliably deliver 90-95% of energy from output signal17into zone5. Neither concentration of energy from output signal17into a small zone5, nor this degree of efficiency, were achievable with previously available alternatives. IMN11reduces reflection of applied output signal17from surface6thereby increasing efficiency of delivery of energy to energy dissipation zone5.

System30may be operated to heat a volume of biological tissue beneath the biological tissue surface6such that surface6of biological tissue4is maintained at a lower temperature than predetermined energy dissipation zone5without a cooling device.

Further, the absence of a ground electrode from system30permits free propagation of the waves of output RF power signal17in energy dissipation zone5.

These factors serve to greatly increase the degree of heating of water molecules1relative to the degree of heating of water molecules1achieved with prior art alternatives.

The inherent advantages of system30are clear from comparison of thermo-grams of energy dissipation zone5using system30(FIG. 4) and a prior art bipolar (i.e. 2 electrode) system (FIG. 5). Each thermo-gram is accompanied by a key on the left which indicates that the colors white, yellow, orange, red, green, blue and violet represent concentrations of heat energy in decreasing order. In each figure, an apple slice is used as biological tissue4.

FIG. 4clearly shows that when applicator3of system30is contacted with surface6of tissue4, delivery of output energy17results in delivery of energy primarily to zone5. Line26passes through the center of zone5. In the example ofFIG. 4, the temperature at surface6of tissue4is clearly lower than along line26in zone5.

In sharp contrast,FIG. 5clearly shows that when applicator3of a prior art bipolar system is contacted with surface6of tissue4, delivery of output energy17results in delivery of energy primarily to a zone5which is adjacent to surface6of tissue4. This reduces the distance between line26, which passes through the center of zone5, and surface6. In other words, the prior art bipolar system delivers heat energy primarily in proximity to surface6. The thermo-gram ofFIG. 5illustrates a distribution of heat energy observed when the prior art bipolar system is operated with a cooling system.

Optionally, but preferably, system30further includes a PWM controller, the PWM controller12capable of causing the RF energy source to deliver the output power signal in pulses of a predetermined duration and amplitude with a desired frequency. For example, the operating RF-frequency is 40.68 MHz, a PWM-frequency is 1 to 20 kHz and a duty cycle is 10 to 90%.

According to some preferred embodiments of the invention, applicator3is made from metals such as, for example, aluminum, silver, gold, copper or alloys thereof. Alternately, or additionally, a dielectric barrier2may be positioned between applicator3and surface6of biological tissue4. Dielectric barrier2prevents unwanted transmission of a conductive current to tissue4. According to some preferred embodiments of the invention, dielectric barrier2is supplied as a dielectric coating on applicator3. According to a most preferred embodiment, applicator3is constructed primarily of aluminum and dielectric barrier2is supplied as an alumina coating.

Optionally, but preferably, applicator3is movable on surface6of biological tissue4as a means of altering a location of energy dissipation zone5.

Optionally, but preferably, system30further includes a feeding cable7, the feeding cable7connecting RF-applicator3and the RF-resonator13with IMN11. Optionally, but preferably, feeding cable7has a resonance length defined by n*λ/2 length, where λ is a wavelength of RF-energy in the cable material and n is a whole number.

Optionally, but preferably, IMN11includes a fixed structure characterized by a shape such as, for example, L shaped, T shaped or Π-shaped structure. Optionally, but preferably, IMN11includes a broadband impedance transformer. Optionally, but preferably, IMN11is variable.

Optionally, but preferably, phase shifter14includes a trombone type phase shifting mechanism.

Alternately, or additionally, phase shifter14may be at least partially constructed of coaxial cable.

Optionally, but preferably, phase shifter14provides a variable phase shift.

Optionally, but preferably, the energy delivered to the predetermined energy dissipation zone5is coupled in a continuous or a pulsing mode. RF-generator10produces output17in the form of a sinusoidal signal which may be modulated by rectangular pulses with lower frequency. This may be accomplished, for example, by PWM controller12.

According to one most preferred embodiment of the invention, system30employs RF-energy17which is characterized by a resonance frequency that matches a known natural resonance frequency of the selected target

Optionally, but preferably, system30may further include additional components, such as, for example, a laser beam, an ultrasonic transducer, a UV light source, a plasma treatment device and a flash lamp.

The present invention is further embodied by an improved method100for thermal treatment of a selected target within a subject. Method100includes:providing102output RF power signal17directed to applicator3contactable with surface6of biological tissue4belonging to the subject.

Method100includes employing104a phase shifter14to shift a phase of RF-traveling waves of output RF power17so that energy therefrom is concentrated primarily in predetermined energy dissipation zone5which lies at a desired depth beneath surface6of biological tissue4. The selected target is positioned within energy dissipation zone5.

Method100further includes converting106impedance of biological tissue4belonging to the subject from a nominal value to a corrected value. The corrected value matches a characteristic impedance characteristic of RF energy source and RF transmission line including a cable11and a phase shifter14so that output RF-traveling wave17may pass through surface6of biological tissue4without being converted to a standing wave by means of IMN11;

Method100further includes cyclically108accumulating/releasing in an RF resonator13located in applicator3the desired amount of energy.

Method100further includes concentrating110the desired amount of energy in RF resonator13so that a significant portion thereof is concentrated in the predetermined energy dissipation zone5upon release from resonator13.

Method100further includes conveying112output17from RF energy source10through surface6of biological tissue4to predetermined energy dissipation zone5after output17has been processed by the phase shifter14, the IMN11and resonator13by means of applicator3.

Performance of102,104,105,108,110and112heats biological tissue beneath the tissue surface6of biological tissue4so that the biological tissue surface6is maintained at a lower temperature than predetermined energy dissipation zone5without requiring a cooling device.

The absence of a ground electrode permits free propagation of the waves in output signal17in energy dissipation zone5.

According to still further features in the described preferred embodiments the providing indicates provision118of output signal17in pulses of a predetermined duration and an amplitude with a desired frequency as detailed hereinabove.

Preferably, method100further includes moving122applicator3with respect to surface6of biological tissue4as a means of altering a location of energy dissipation zone5.

Optionally, but preferably, method100further includes employing124a feeding cable XX to connect applicator3, and resonator11with IMN11.

Optionally, but preferably, method100further includes varying126the phase shift provided by phase shifter14.

Method100is optimally employed for cellulite treatment by selecting a predetermined energy dissipation including at least one cellulite body which serves as a target which is heated to a greater degree than tissue adjacent thereto. As a result, cellulite is reduced128.

The present invention relies upon RF-heating of biological tissues via rotation of molecules of the water molecules1(FIG. 1), which are dipole structures, in an alternating electromagnetic field. In order to avoid a conductive HF-current a dielectric barrier2provides insulation between the applicator3and a biological tissue surface6.

Preferably, applicator3is constructed from aluminum or an aluminum alloy covered by alumina coating with a thickness 40-50 μm.

Applicator3can be also described as an antenna coupler that irradiates the RF-wave into deep tissue4. The resultant dissipation of the energy load can be described as irradiative coupling of RF-energy.

The area through which applied RF energy is primarily applied5is determined by the contact area between tissue surface6and applicator3and by the phase of incident electromagnetic wave pulses17. The energy diverges from surface6and is effectively dissipated5through tissue4. The depth of RF-energy penetration depends on RF-power and area of applicator and phase shift of electromagnetic wave. By application of phase shifting device14it is possible to adjust a position of energy dissipation zone5and to coincide with a selected target (e.g. cellulite lesions).

The applied oscillating RF-field stimulates all dipole molecules (mostly water molecules1) to rotate and vibrate with consequent heating of energy dissipation zone5. Zone5may be controlled by phase shifting device14between RF-generator10and applicator3. Heating will be primarily in adipose tissue because it is rich in liquids but not subject to convective cooling as blood vessels are. The pulse width modulation (PWM) control12of output RF-power that provide a possibility to keep a high peak RF-power with low average power level.

The absence of a second or ground electrode in the pictured configuration permits free propagation of RF waves inside tissue4.

In order to maximize transmission of RF-energy from RF-source10(FIG. 2) through resonant cable7to applicator3, it is connected to the central point of a parallel resonator13including a capacitor8and an inductor9connected in parallel and characterized by very high-Q-factor for example more than 20.

The delivered oscillating RF-power (e.g. 25-300 watts) is stored in the resonator13therefore an active (dissipative) load of resonator13is only an adjacent tissue.

The active losses of resonator13are very low (20-50 times less than energy dissipated inside tissue4). The intermittent discharge of capacitor18and the inductor19is coupled through applicator3to tissue4.

RF-generator10capable of producing 200-400 Watts full power at 40.68 MHz operating frequency demonstrates an optimal performance at 50 Ohms resistive load. Optimal performance means minimal reflected RF-power with maximum RF-forward power dissipated by a load. Thus, the real load that includes treated volume5of tissue4is matched as 50 Ohms load.

The used impedance matching network (IMN11; seeFIG. 2) is fixed (the elements are not variable operatively); therefore operation occurs without RF-power amplitude changes. The control of output power is reached by PWM-control (pulse width modulation). PMW achieves modulation of output power by rectangular power pulses applied with a frequency lower than that of the RF wave. In order to decrease RF-power coupling it is necessary to reduce a duty cycle of PWM. PWM-controller12produces rectangular pulses with a modulation frequency range of 2-10 kHz. The duty cycle may be varied from 5 to 100%. The shape of RF-power pulse17is showed inFIG. 2. The PWM-control of output RF-power permits high peak RF-power level in heating zone5with lower average power. This provides efficient heating of adipose capsules with minimal impact on blood vessels and other tissues.

The reflected RF-power is 1-2% of output power therefore 98% of output power is dissipated in the treated volume. Typically, we concentrate energy in adipose tissue therefore coupled RF-energy is dissipated by fat cells, cellulite capsules and by blood and lymphatic liquids. The energy that produces a useful job in fat cells and cellulite tissue will reach 70-80% of total energy coupled to the volume. The rest energy is dissipated through diffusion of the heat to the surface and by convection of natural liquids of human body.

Applicator3is connected to parallel resonator13. Applicator3and resonator13are physically positioned inside of operating hand-piece22used for treatment procedure. The IMN-system locates inside the main system23. In order to avoid a mismatching phase shift between the applicator3and the IMN11, the length of cable7is equal to the whole number (n) of wavelength of RF-energy (λ) in the cable material.

In order to reach necessary amplitude under the surface6of tissue4, a phase shifting system (e.g. trombone-type system14) is inserted between output of RF-generator10and an input of IMN11. The position of the maximum of energy dissipation can be controlled by this phase shifting system. In order to control the depth of RF-energy penetration the length of trombone can be shortened that change a position of dissipated electromagnetic wave in the tissue or an area of the maximum of RF-voltage. Consequently, RF-energy will be dissipated most efficiently in the volume around maximum of the RF-voltage.

The phase shifter14can be controlled automatically, for example by motors15. This change of phase could be linear or periodical that provides a displacement of maximal heating zone inside the tissue or scanning of maximal heating zone position.

The practical implementation of impedance matching system11is illustrated byFIG. 3. The RF-power delivered from RF-generator10through coaxial cable16is modulated by rectangular pulses17. Because RF-generator10is matched to 50 Ohms and impedance of human tissue is close to 300 Ohms, it is necessary to convert 50 to 300 Ohms with compensation of electromagnetic reactance of tissue4. This is achieved with impedance matching network11. L-type simple fixed IMN consisting of RF-capacitor18and RF-inductor19(FIG. 3) were applied for this purpose. Half-wave cable7is applied for transmission of RF-energy from IMN11to RF applicator3without phase shifting that is controllable by phase shifting system. The measured impedance in the point20is 50 Ohms and in the point21is 300 Ohms. Impedance matching networks of various types may be employed without significantly altering performance of the present invention. Regardless of the exact IMN type employed, the IMN11can be variably and/or automatically controlled to trace an impedance changing.