Systems and methods for simultaneous multi-focus ultrasound therapy in multiple dimensions

Abstract

Embodiments of skin cosmetic treatment and / or imaging systems and methods are adapted to alter the placement and position of multiple cosmetic treatment areas in tissue from an ultrasound beam from a transducer, to perform simultaneous multifocal treatment at multiple depths, and / or to vibrate the ultrasound beam from the transducer to alter the placement and position of multiple cosmetic treatment areas in tissue. The system may include a handheld stick, a removable transducer module, and a control module. In some embodiments, the cosmetic treatment system can be used in various cosmetic procedures.

Description

Systems and methods for simultaneous multi-focused ultrasound therapy in multiple dimensions Several embodiments of the present invention relate to non-invasive, energy-based treatments for achieving aesthetic and / or cosmetic enhancement effects on the skin and / or tissue adjacent to the skin of a person's face, head, neck, and / or body by delivering energy simultaneously or nearly simultaneously to multiple dimensions (e.g., depth, height, width, spacing, orientation, placement) of tissue beneath the skin's surface. Incorporated by Reference The entire contents of U.S. Provisional Patent Application No. 62 / 622,394, filed January 26, 2018, are incorporated herein by reference for all purposes. Some cosmetic procedures involve invasive procedures that may require surgical intervention. Patients not only have to endure weeks of recovery time, but are often required to undergo dangerous anesthesia. Non-invasive energy-based treatment devices and methods are available, but they can have various drawbacks in terms of efficiency and effectiveness. In several embodiments, systems and methods are provided for successfully achieving aesthetic results using targeted and precise ultrasound. These methods produce visible and effective cosmetic effects via a thermal path by splitting the ultrasound treatment beam into two, three, four, or more simultaneous focal zones for various therapeutic and / or imaging procedures. In various embodiments, the ultrasound system is configured to focus ultrasound to induce localized mechanical motion within tissue and cells, thereby generating localized heating for tissue coagulation or mechanical cell membrane disruption for non-invasive aesthetic applications. In various embodiments, the ultrasound system is configured for brow lifts (e.g., brow lifts). In various embodiments, the ultrasound system is configured to lift tissue that is lax, sagging, or sagging, such as tissue under the chin and neck. In various embodiments, the ultrasound system is configured to improve neck lines and wrinkles. In various embodiments, the ultrasound system is configured to reduce fat. In various embodiments, the ultrasound system is configured to reduce the appearance of cellulite. In some embodiments, a system is provided for reducing fat and subsequently treating sagging skin caused by fat reduction. While various embodiments are contemplated herein for use in cosmetic treatments, in some embodiments, the systems and programs described herein are also used in non-aesthetic applications. In various embodiments, the ultrasound system is configured for imaging to visualize tissue (e.g., dermis and subcutaneous layers of tissue) to ensure proper coupling of the transducer to the skin. In various embodiments, the ultrasound system is configured for imaging to visualize tissue (e.g., dermis and subcutaneous layers of tissue) to confirm proper treatment depth to avoid certain tissues (e.g., bone). In various embodiments, treating tissue (e.g., skin tissue) with multiple beams provides one or more advantages, such as reducing treatment time, creating unique heating patterns, utilizing multiple channels for greater power, the option to treat the skin at two or more depths with the same or different power levels (e.g., a thermal coagulation point in the superficial musculoaponeurotic system ("SMAS") and another defocused energy at the skin surface, or other combinations), optional simultaneous treatment at different depths (e.g., at depths below the skin surface of 1.5 mm, 3 mm, and / or 4.5 mm thermal coagulation points simultaneously or within overlapping time periods); and / or treating with one, two, or more simultaneous linear or line-focused beams, such as at different depths below the skin surface or spaced apart. In some embodiments, the simultaneous multifocal treatment uses dithering. According to one embodiment, an ultrasound therapy system creates two or more simultaneous treatment points and / or focal areas beneath the skin surface for cosmetic treatment, wherein the treatment point is enlarged by dithering the ultrasound beam. In one embodiment, the focal area is a point. In one embodiment, the focal area is a line. In one embodiment, the focal area is a plane. In one embodiment, the focal area is a three-dimensional volume or shape. Dithering the ultrasound beam focus enlarges the treatment area by changing the frequency of the ultrasound therapy beam, and thus the focus, by mechanically and / or electronically dispersing the focus position. This dithering can be achieved by causing the focus or focal area (e.g., a focal point, line, plane, or volume) to sway, blur, or splatter like paint using an airbrush. In some embodiments, dithering increases efficacy by creating a larger treatment point and / or focal area. In some embodiments, dithering reduces pain because the temperature of the hotspot is distributed over a larger volume of tissue, potentially allowing for dose reduction. In some embodiments, mechanical dithering is a method of spreading the acoustic energy from the ultrasound beam, thereby reducing reliance on thermal conduction from tissue away from the focal point. In one embodiment of mechanical dithering, the therapy transducer is locally moved around the desired center of the thermal coagulation point (TCP). The beam movement can be side-to-side, up-and-down, and / or angled. In one embodiment of mechanical dithering, the movement of the motion mechanism is fast enough to produce a flatter temperature distribution around the intended TCP, which allows for a reduction in total acoustic energy for the same affected tissue volume or the same total acoustic energy for a larger affected tissue volume, or any combination thereof. According to various embodiments, frequency modulation modifies the position of the focal regions and / or the spacing between the focal regions, such that the position of the beam focus is precisely altered and / or moved via frequency modulated electronic dithering of the beam. For example, in one embodiment, a 1.5 mm spacing can be dithered by + / - 0.1 mm using a small frequency wobble. In various embodiments, any one or more spacings of 0.5, 0.75, 1.0, 1.2, 1.5, 2.0 mm can be dithered by + / - 0.01, 0.05, 0.1, 0.12, 0.15, 0.20, 0.25, 0.30 mm using a frequency wobble. In various embodiments, the frequency is modulated by 1-200% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 100%, 120%, 150%, 180%, 200%, and any ranges therein). Several embodiments relate to apparatus, systems, and methods for providing one or more (e.g., multiple or many) focal regions and / or ultrasound treatment points to quickly, safely, efficiently, and effectively perform various ultrasound treatment and / or imaging procedures. In some embodiments, imaging is not used. Some embodiments relate to splitting an ultrasound treatment beam from a single ultrasound transducer and / or a single ultrasound transducing element into two, three, four, or more focal regions. In some embodiments, multiple ultrasound beams are electronically steered using frequency modulation. In some embodiments, dithering (e.g., electronic dithering) of the apertures of the multiple and / or split ultrasound beams using frequency modulation is used to provide treatment regions or points in multiple locations. In some embodiments, dithering involves intentionally shifting the position / location of the focal point of the energy beam. For example, in one embodiment, dithering involves shaking, moving, vibrating, or changing the position and / or location of a single focal region and / or the relative spacing between two or more focal regions. In various embodiments, the relative positions of the focal zones are dithered by 1-50% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any range therein, such as a percentage of a certain percentage of the average position). In various embodiments, the spacing between the focal zones is dithered by 1-50% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any range therein). In some embodiments, dithering can be achieved mechanically, electronically, or by a combination of mechanical and electronic means, depending on the system design. In one embodiment of mechanical dithering, the ultrasound beam is locally moved around the center of the intended TCP by mechanical translation or tilting of the therapy transducer or the patient, or any combination thereof. Mechanical translation and / or tilting can achieve a spread of the acoustic energy such that thermal conductivity limitations of the tissue are overcome. Compared to a fixed ultrasound therapy device, this produces a flatter temperature distribution in the tissue to reduce the total acoustic energy to produce the same affected tissue volume or to have the same total acoustic energy to increase the affected tissue volume. In various embodiments of electronic dithering, frequency, phase, amplitude modulation, or time-based techniques are used in combination with a uniquely defined transducer to move the ultrasound beam in the tissue without any mechanical movement. In one embodiment, the electronic movement of the ultrasound beam is significantly faster than mechanical movement to overcome the thermal conductivity limitations of the tissue. In various embodiments, the ratio of relative focal area positioning via dithering is 1:1000, 1:500, 1:200, 1:100, 1:50, 1:25, 1:10, 1:2, or any ratio between 1:1000 and 1:1. In various embodiments, the ratio of the spacing between relative focus region positions via dithering is 1:1000, 1:500, 1:200, 1:100, 1:50, 1:25, 1:10, 1:2, or any ratio between 1:1000 and 1:1.For example, in some embodiments, a focal zone is activated at "1," and the ratio of the open interval to the untreated tissue is provided in the second digit of the ratio. For example, in one embodiment, the dithering interval is, for example, 1 mm, and the dithering distance is 0.1 mm, resulting in a ratio of 1:10. In various embodiments, the ratio of the spacing between the focal zones via dithering is 1:1000, 1:500, 1:200, 1:100, 1:50, 1:25, 1:10, 1:2, or any ratio between 1:1000 and 1:1. In some embodiments, the spacing of the focal zones is simultaneously dithered. In some embodiments, treatment points and / or zones are simultaneously formed in the tissue. In various embodiments, the dithering used to perform various treatments and / or imaging procedures is modulated and / or polyphasic, with controlled frequency variation. Some embodiments involve splitting the ultrasound treatment beam into two, three, four, or more focal zones for performing various treatments and / or imaging procedures, for example, using dithering, polarization, phasing, and / or modulation techniques. In several embodiments disclosed herein, the non-invasive ultrasound system is suitable for use in achieving one or more of the following beneficial aesthetic and / or cosmetic improvements: face lift, brow lift, chin lift, eye treatment (e.g., zygomatic bags, treatment of infraorbital laxity), wrinkle reduction, fat reduction (e.g., treatment of fat and / or cellulite), treatment of cellulite (which may be referred to as female lipodystrophy) (e.g., concave or non-concave female lipodystrophy), shoulder enhancement (e.g., upper chest), buttock lift (e.g., buttock tightening), skin tightening (e.g., treatment of laxity to result in facial or body tightening, such as the face, neck, chest, arms, thighs, abdomen, buttocks, etc.), scar reduction (e.g., reduction of breast cystic fibrosis), burn treatment, tattoo removal, vein removal, vein reduction, treatment of sweat glands, treatment of hyperhidrosis, sunspot removal, acne treatment, and pimple reduction. Several embodiments of the present invention are particularly advantageous because they include one, several, or all of the following benefits: (i) faster treatment time, (ii) less pain during treatment, (iii) less pain after treatment, (iv) shorter recovery time, (v) more efficient treatment, (vi) higher customer satisfaction, (vii) less energy required to complete treatment, and / or (viii) a larger treatment area provided by a dithered focal zone. Advantages of embodiments of a simultaneous multi-depth treatment device configured to produce multiple TCPs at various depths include producing simultaneous TCPs at multiple depths. In one embodiment, an advantage is the elimination of multiple transducers, thereby reducing transducer swapping by the operator. In one embodiment, an advantage is faster treatment time. In one embodiment, an advantage is delivering the same number of lines with fewer button presses. In one embodiment, an advantage is modulation of the distance between simultaneously delivered TCPs. In one embodiment, an advantage is maintaining the pitch separation of TCPs at each depth along the line of mechanical motion. In one embodiment, an advantage is avoiding pulse stacking at multiple depths. In one embodiment, an advantage is the ability to produce larger coagulation and apoptosis zones. In one embodiment, an advantage is the ability to deliver microcoagulation lines in three dimensions. In one embodiment, an advantage of using an electrostrictor includes generating more than two lines with a single transducer placed on the patient's body. In one embodiment, an advantage of using an electrostrictor is modulating the distance between simultaneously delivered TCPs. In one embodiment, an advantage is the ability to modulate spatial high-frequency harmonics from the simultaneous treatment modulation pattern. In one embodiment, an advantage of using an electrostrictor provides the possibility of adding nulls to the modulation pattern. In one embodiment, an advantage of using an electrostrictor is effectively modulating the distance between simultaneously delivered TCPs while simultaneously electronically steering and focusing opposing surfaces.This can be in the form of strips, annular rings, and segments that are orthogonal to (or at any angle relative to each other, such as 0° to 180° (5°, 10°, 15°, 20°, 30°, 45°, 60°, 90°, or more)) the electrostrictor strip. In various embodiments, the transducer is segmented. In various embodiments, the flat transducer can be focused with a lens. In various embodiments, the transducer is spherically focused to one or more points. In various embodiments, the transducer is cylindrically focused to one or more lines. According to various embodiments, cosmetic ultrasound treatment systems and / or methods can non-invasively generate single or multiple vibrating cosmetic treatment zones and / or thermal coagulation points, where ultrasound is focused at one or more locations within the treatment zone in tissue beneath the skin's surface and moved via frequency variation (e.g., via frequency modulation). Some systems and methods provide cosmetic treatment at different locations within the tissue, such as at different depths, heights, widths, and / or positions. In one embodiment, a method and system includes a multi-depth / height / width transducer system configured to provide ultrasound treatment to one or more regions of interest, such as between at least one depth of the treatment zone of interest, a surface zone of interest, and / or a subcutaneous zone of interest. In one embodiment, a method and system includes a transducer system configured to provide ultrasound treatment to more than one region of interest, such as between at least two points at various locations within the region of interest in tissue (e.g., at one or more fixed or variable depths, heights, widths, and / or orientations, etc.). Some embodiments can split the beam to focus at two, three, four, or more focal points (e.g., multiple focal points, multifocal points) for cosmetic treatment areas and / or for imaging regions of interest in tissue. The position and / or dithering of the focal points can be positioned axially, laterally, or otherwise within the tissue. Some embodiments can be configured for spatial control, such as by varying the distance from the transducer to the reflective surface and / or the angle of energy focused or unfocused onto the region of interest through the position and / or dithering of the focal points, and / or for temporal control, such as by varying the frequency, drive amplitude, and timing of the transducer. In some embodiments, the position and / or dithering of multiple treatment regions or focal points is achieved using polarization, phase polarization, dual-phase polarization, and / or multi-phase polarization. In some embodiments, the position and / or dithering of multiple treatment regions or focal points is achieved using phasing, such as, in one embodiment, electrical phasing. As a result, the position of the treatment regions, the number, shape, size, and / or volume of treatment regions or lesions within the region of interest, and thermal conditions can be dynamically controlled over time. According to various embodiments, a cosmetic ultrasound treatment system and / or method can generate multiple cosmetic treatment zones using one or more of frequency modulation, phase modulation, polarization, nonlinear acoustics, and / or Fourier transforms to create any spatially periodic pattern using one or more ultrasound segments. In one embodiment, the system uses polarization at the ceramic level to deliver single or multiple treatment zones simultaneously or sequentially. In one embodiment, the polarization pattern depends on the depth of focus and frequency, as well as the use of odd or even functions. In one embodiment, a polarization pattern is applied that can be a combination of odd or even functions, based on the depth of focus and / or frequency. In one embodiment, processes can be used in two or more dimensions to create any spatially periodic pattern. In one embodiment, the ultrasound beam is split axially and transversely using nonlinear acoustics and Fourier transforms to significantly reduce treatment time. In one embodiment, modulation from the system and amplitude modulation from the ceramic or transducer can be used to place multiple treatment zones in tissue sequentially or simultaneously. In one embodiment, an aesthetic imaging and treatment system includes an ultrasound probe including an ultrasound transducer configured to apply ultrasound therapy to tissue at multiple locations within a focal depth by electronically dithering multiple energy beam apertures through frequency modulation. In one embodiment, the system includes a control module coupled to the ultrasound probe for controlling the ultrasound transducer. In one embodiment, the system includes a dithering mechanism configured to provide variable spacing between a plurality of individual cosmetic treatment areas. In one embodiment, the sequence of individual cosmetic treatment areas has a treatment spacing in the range of about 0.01 mm to about 25 mm (e.g., 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 5 mm, 10 mm, 20 mm, and any range thereof), with the spacing being varied by a dithering of 1-50% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any range thereof). In one embodiment, the sequence of individual cosmetic treatment areas has a treatment interval in the range of about 0.01 mm to about 100 mm (e.g., 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 5 mm, 10 mm, 20 mm, 25 mm, 30 mm, 35 mm, 40 mm, 45 mm, 50 mm, 60 mm, 70 mm, 80 mm, 90 mm, and 100 mm, and any ranges therein), with a jittered variation of the intervals of 1-50% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any ranges therein). In one embodiment, the system further comprises a movement mechanism configured to be programmed to provide a constant or variable spacing between the plurality of individual cosmetic treatment areas. In one embodiment, the sequence of individual cosmetic treatment areas has a treatment spacing in the range of about 0.01 mm to about 50 mm (e.g., 0.1, 0.5, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 19, 20, 25, 30, 35, 40, 45, 49 mm, or any range or value therein). In one embodiment, the sequence of individual cosmetic treatment areas has a treatment spacing in the range of about 0.01 mm to about 100 mm (e.g., 0.1, 0.5, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 25, 30, 35, 40, 50, 100 mm, or any range or value therein). In one embodiment, the treatment areas are provided along a distance of about 25 mm. In one embodiment, the treatment areas are provided along a distance of about 50 mm. In various embodiments, the treatment area is provided along a distance of 5 mm to 100 mm (e.g., 10 mm, 20 mm, 25 mm, 35 mm, 50 mm, 75 mm, 100 mm, and any amount or range therein). In various embodiments, the treatment area is provided along a linear and / or curved distance. For example, in some non-limiting embodiments, the transducer can be configured for tissue depths of 0.5 mm, 1.0 mm, 1.5 mm, 2 mm, 3 mm, 4.5 mm, 6 mm, less than 3 mm, between 0.5 mm and 5 mm, between 1.5 mm and 4.5 mm, greater than 4.5 mm, greater than 6 mm, and within the range of 0.1 mm to 3 mm, 0.1 mm to 4.5 mm, 0.1 mm to 25 mm, 0.1 mm to 100 mm, and any depth therein (e.g., 6 mm, 10 mm, 13 mm, 15 mm, 17 mm). In several embodiments, tissue is treated at a depth below the skin surface without damaging the skin surface. Rather, the therapeutic effect achieved at a depth below the skin surface results in a favorable cosmetic appearance of the skin surface. In other embodiments, the skin surface is treated with ultrasound (e.g., at a depth of less than 0.5 mm). One benefit of a motion mechanism is that it can provide more efficient, accurate, and precise use of ultrasound transducers for imaging and / or therapeutic purposes. An advantage of this type of motion mechanism over conventional fixed arrays of multiple transducers fixed in space within a housing is that the fixed arrays are separated by a fixed distance. In one embodiment, the transducer module is configured to provide therapeutic ultrasound acoustic power in the range of approximately 1 W to approximately 100 W, or 100 W to 1000 W (e.g., 3-30 W, 7-30 W, 21 W-33 W, 200 W, 500 W, 750 W, 900 W), or higher, and a frequency of approximately 1 MHz to approximately 20 MHz to thermally heat tissue to induce coagulation. In one embodiment, the transducer module is configured to provide therapeutic ultrasound acoustic power in the range of approximately 1 W to approximately 500 W (e.g., 3-30 W, 7-30 W, 21-33 W, 100 W, 220 W, or higher) and a frequency of approximately 1 MHz to approximately 20 MHz to thermally heat tissue to induce coagulation. In some embodiments, instantaneous energy is delivered. In some embodiments, average energy is delivered. In one embodiment, the acoustic power can range from 1 W to 100 W within a frequency range of about 1 MHz to about 20 MHz (e.g., 1 MHz, 3 MHz, 4 MHz, 4.5 MHz, 7 MHz, 10 MHz, 2-12 MHz, 15 MHz, 18 MHz, 2-18 MHz), or from about 10 W to 50 W within a frequency range of about 3 MHz to about 8 MHz (e.g., 3 MHz, 4 MHz, 4.5 MHz, 7 MHz). In one embodiment, the acoustic power can range from 1 W to 500 W within a frequency range of about 1 MHz to about 12 MHz (e.g., 1 MHz, 4 MHz, 7 MHz, 10 MHz, 2-12 MHz), or from about 10 W to about 220 W within a frequency range of about 3 MHz to about 8 MHz or 3 MHz to 10 MHz. In one embodiment, the acoustic power and frequency are about 40 W at about 4.3 MHz and about 30 W at about 7.5 MHz. The acoustic energy generated by the acoustic power can be between about 0.01 joules ("J") and about 10 J or about 2 J to about 5 J. The acoustic energy generated by the acoustic power can be between about 0.01 J and about 60,000 J (e.g., via torso heating for body contouring, submental fat, abdomen and / or flanks, arms, inner thighs, outer thighs, buttocks, abdominal laxity, cellulite), about 10 J or about 2 J to about 5 J. In some embodiments, the acoustic energy is in the range of less than about 3 J. In various embodiments, the treatment power is 1 kW / cm 2 Up to 100kW / cm 2 、15kW / cm 2Up to 75kW / cm 2 , 1kW / cm 2 Up to 5kW / cm 2 , 500W / cm 2 Up to 10kW / cm 2 、3kW / cm 2 Up to 10kW / cm 2 、15kW / cm 2 Up to 50kW / cm 2 , 20kW / cm 2 Up to 40kW / cm 2 and / or 15kW / cm 2 Up to 35kW / cm 2 . In various embodiments, an ultrasound therapy system for dithering multiple simultaneous focal points from an ultrasound transducer includes an ultrasound probe and a control module coupled to the ultrasound probe for controlling the ultrasound transducer. The ultrasound probe includes an ultrasound transducer having a single transducer element adapted to simultaneously deliver ultrasound therapy to tissue at multiple spaced locations within a focal depth. The ultrasound transducer is polarized with at least a first polarization configuration and a second polarization configuration. The control module modifies the spacing between the spaced locations via dithering of the first and second focal regions, thereby precisely shifting the position of the beam focus at the spaced locations via frequency-modulated dithering. In one embodiment, the plurality of locations are positioned within the cosmetic treatment area in a linear sequence, with the alternate locations separated by intervals via frequency wobble dithering. In one embodiment, a first set of locations are positioned within a first cosmetic treatment area, and a second set of locations are positioned within a second cosmetic treatment area, the first area being different from the second area. In one embodiment, the ultrasonic transducer is adapted to apply the ultrasonic treatment using amplitude modulation, whereby the plurality of portions of the ultrasonic transducer are adapted to emit the ultrasonic treatment at a plurality of acoustic intensity amplitudes, whereby the first amplitude is different from the second amplitude. In one embodiment, at least a portion of the ultrasonic transducer is adapted to emit the ultrasonic treatment at two or more acoustic intensity amplitudes, and whereby the amplitude of the ultrasonic treatment emitted by at least a portion of the piezoelectric element varies over time. In one embodiment, the ultrasonic transducer comprises a piezoelectric material, and the plurality of portions of the ultrasonic transducer are adapted to generate a plurality of corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer. In one embodiment, the plurality of piezoelectric material changes comprise at least one of expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, the ultrasonic transducer is adapted to apply the ultrasonic treatment via phase shifting, whereby the plurality of portions of the ultrasonic transducer are adapted to emit the ultrasonic treatment at a plurality of acoustic intensity phases, whereby the first phase is different from the second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the ultrasonic transducer is adapted to apply ultrasonic therapy using amplitude modulation, whereby the plurality of portions of the ultrasonic transducer are adapted to transmit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude, and to apply ultrasonic therapy, whereby the plurality of portions of the ultrasonic transducer are adapted to transmit ultrasonic therapy at a plurality of acoustic intensity phases, wherein a first phase is different from the second phase. In some embodiments, skin tightening is achieved by reducing skin laxity to treat subjects with excess or loose skin after weight loss, whether such weight loss occurred naturally or was achieved through surgery. In various embodiments, an ultrasound therapy system for dithering multiple simultaneous focal points from an ultrasound transducer during cosmetic treatment includes an ultrasound probe, the ultrasound probe including a control module adapted to modify the spacing between a first focal region and a second focal region via dithering, a switch operable to control an ultrasound therapy function for providing ultrasound therapy, a movement mechanism adapted to direct the ultrasound therapy in at least one pair of simultaneous sequences of separate thermal cosmetic treatment zones, and a transducer module adapted to apply the ultrasound therapy. The transducer module is adapted to be coupled to the ultrasound probe. The transducer module includes an ultrasound transducer adapted to apply the ultrasound therapy to tissue at multiple locations within a focal depth. The transducer module is adapted to be operably coupled to at least one of the switch and the movement mechanism. The control module includes a processor and a display for controlling the transducer module. In one embodiment, the transducer module is adapted to apply ultrasonic therapy using amplitude modulation, whereby portions of the transducer module are adapted to transmit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the transducer module is adapted to apply ultrasonic therapy, whereby portions of the transducer module are adapted to transmit ultrasonic therapy at a plurality of acoustic intensity phases, wherein a first phase is different from a second phase. In various embodiments, a system for ultrasonic therapy with dithered multifocal therapy includes a module having an ultrasonic transducer adapted to simultaneously apply ultrasonic therapy to tissue at a plurality of spaced locations therein, wherein the module modulates the spacing between the plurality of spaced locations via dithering of a first focal region and a second focal region, thereby precisely shifting the position of a beam focus at the plurality of spaced locations via frequency-modulated dithering, and wherein the module further includes an interface guide designed to be removably coupled to a handheld wand to provide electronic communication and power between the module and the handheld wand. In one embodiment, the ultrasonic transducer is adapted to apply ultrasonic therapy using amplitude modulation, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic therapy at multiple acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the ultrasonic transducer is adapted to apply ultrasonic therapy, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic therapy at multiple acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the ultrasonic transducer includes a piezoelectric material, and the multiple portions of the ultrasonic transducer are adapted to generate multiple corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer. In one embodiment, at least a portion of the ultrasonic transducer is adapted to emit ultrasonic therapy at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the ultrasonic transducer remains constant over time. In one embodiment, the ultrasound treatment is a face lift, brow lift, chin lift, eye treatment (e.g., cheekbone bags, treatment of infraorbital laxity), wrinkle reduction, shoulder enhancement, butt lift, scar reduction, burn treatment, tattoo removal, skin tightening (e.g., tummy tuck treatment or tightening of skin in other areas of the body and face, such as any excess skin or tissue, such as during or after weight loss, e.g., the abdomen, buttocks, thighs, arms, and other areas), vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sun spot removal, fat treatment, vaginal rejuvenation, and acne treatment. In various embodiments, a method of dithering a simultaneously focused ultrasound therapy beam includes providing an ultrasound probe including an ultrasound transducer including a single transducer element adapted to simultaneously apply ultrasound therapy to tissue at a plurality of spaced locations within a focal depth, and a control module coupled to the ultrasound probe for controlling the ultrasound transducer and dithering a spacing between spaced locations of a first focal region and a second focal region via a modulated frequency to move a position of the ultrasound focus at the spaced locations. In one embodiment, the method includes imaging a first focal region with an ultrasonic imaging element. In one embodiment, the method includes imaging a second focal region with an ultrasonic imaging element. In one embodiment, the spacing between the first focal region and the second focal region is dithered within a range of 1-50%. In one embodiment, the spacing between the first focal region and the second focal region is 1.5 mm with a fluctuation of 0.1 mm. In one embodiment, the frequency modulation is within a range of 1-50%. In various embodiments, a method of dithering a focused ultrasound beam includes providing an ultrasound probe including a single transducer element and a control module, wherein the single transducer element is adapted to apply ultrasound treatment to tissue at a focal region at a focal depth, wherein the control module is coupled to the ultrasound probe for controlling the single transducer element and dithering the focal region via a modulated frequency to vary a size of the focal region at the tissue. In one embodiment, the relative position of the focal region is dithered within a range of 1-50%. In one embodiment, the second focal region is simultaneously emitted from a single transducer element. In one embodiment, the method includes imaging the focal region with an ultrasonic imaging element. In one embodiment, the frequency modulation is within a range of 1-50%. In various embodiments, an ultrasound treatment system for generating multiple focal points and varying depths using an ultrasound transducer includes an ultrasound probe, the ultrasound transducer configured to apply ultrasound treatment to tissue at multiple locations having at least two focal depths using at least one of the group consisting of amplitude-modulated polarization and phase shifting, a motion mechanism configured to be programmed to provide spacing between a plurality of individual cosmetic treatment zones, wherein the sequence of individual cosmetic treatment zones has a treatment spacing in the range of 1 mm to 50 mm, and a control module coupled to the ultrasound probe for controlling the ultrasound transducer, wherein the ultrasound transducer is configured to provide ultrasound treatment acoustic power in the range of 10 W to 1000 W and a frequency of 1 MHz to 20 MHz to thermally heat tissue to induce coagulation. In one embodiment, the plurality of locations are positioned in a substantially linear sequence within the cosmetic treatment zone, and the ultrasound transducer includes a single ultrasound transducing element. In one embodiment, a first set of locations is positioned within a first cosmetic treatment zone, and a second set of locations is positioned within a second cosmetic treatment zone, the first zone being different from the second zone. In one embodiment, the first cosmetic treatment area comprises a generally linear sequence of a first set of locations, and the second cosmetic treatment area comprises a generally linear sequence of a second set of locations. In one embodiment, the ultrasonic transducer is configured to apply the ultrasonic treatment using amplitude modulation, whereby portions of the ultrasonic transducer are configured to emit the ultrasonic treatment at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the ultrasonic transducer is configured to apply a therapeutic ultrasound phase shift, whereby multiple portions of the ultrasonic transducer are configured to emit therapeutic ultrasound at multiple acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the ultrasonic transducer is configured to apply the therapeutic ultrasound using amplitude modulation, whereby multiple portions of the ultrasonic transducer are configured to emit therapeutic ultrasound at multiple acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude; and to apply a therapeutic ultrasound phase shift, whereby multiple portions of the ultrasonic transducer are configured to emit therapeutic ultrasound at multiple acoustic intensity phases, wherein the first phase is different from the second phase. In one embodiment, the multiple phases include discrete phase values. In one embodiment, the ultrasonic transducer includes a piezoelectric material, and the multiple portions of the ultrasonic transducer are configured to generate multiple corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer. In one embodiment, the multiple piezoelectric material changes include at least one of expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, at least a portion of the ultrasonic transducer is configured to emit therapeutic ultrasound at two or more acoustic intensity amplitudes, and wherein the amplitude of the therapeutic ultrasound emitted by at least a portion of the piezoelectric varies over time. In one embodiment, the movement mechanism is configured to be programmed to provide variable spacing between a plurality of individual cosmetic treatment areas, and further includes one or more selectable tuning circuits. In one embodiment, the sequence of individual cosmetic treatment areas has a treatment spacing in the range of 1 mm to 25 mm, and further includes a tuning circuit. In one embodiment, the ultrasonic treatment is at least one of a face lift, a brow lift, a chin lift, eye treatment, wrinkle reduction, scar reduction, burn treatment, skin tightening, vein reduction, sweat gland treatment, hyperhidrosis treatment, sun spot removal, fat treatment, cellulite treatment, shoulder treatment, vaginal rejuvenation, and acne treatment. In one embodiment, the ultrasonic transducer is configured to provide ultrasonic treatment acoustic power in the range of 10 W to 100 W and a frequency of 1 MHz to 12 MHz to thermally heat tissue to induce coagulation. In various embodiments, a treatment system for simultaneously generating multiple focal points at different depths using an ultrasound transducer includes an ultrasound probe having a first switch operable to control an ultrasound imaging function for providing ultrasound imaging, a second switch operable to control an ultrasound treatment function for providing ultrasound treatment, and a movement mechanism configured to direct ultrasound treatment in at least one sequence of separate thermal cosmetic treatment areas; and a transducer module configured to apply ultrasound treatment using at least one of the group consisting of amplitude modulation polarization and phase shifting, wherein the transducer module is configured for ultrasound imaging and ultrasound treatment, wherein the transducer module is configured to be coupled to the ultrasound probe, wherein the transducer module includes an ultrasound transducer configured to apply ultrasound treatment to tissue at multiple locations having at least two focal depths, wherein the transducer module is configured to be operably coupled to at least one of the first switch, the second switch, and the movement mechanism; and a control module, wherein the control module includes a processor and a display for controlling the transducer module. In one embodiment, the ultrasonic treatment is a cosmetic treatment wherein the plurality of positions are positioned in a generally linear sequence within a cosmetic treatment area. In one embodiment, the ultrasonic treatment is a cosmetic treatment wherein a first set of positions are positioned within a first treatment area and a second set of positions are positioned within a second treatment area, the first area being different from the second area. In one embodiment, the first treatment area comprises a generally linear sequence of the first set of positions and the second treatment area comprises a generally linear sequence of the second set of positions. In one embodiment, the transducer module is configured to apply the ultrasonic treatment using amplitude modulation, whereby the plurality of portions of the transducer module are configured to emit the ultrasonic treatment at a plurality of acoustic intensity amplitudes, whereby the first amplitude is different from the second amplitude. In one embodiment, the transducer module is configured to apply an ultrasonic treatment phase shift, whereby the plurality of portions of the transducer module are configured to emit the ultrasonic treatment at a plurality of acoustic intensity phases, whereby the first phase is different from the second phase. In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude modulation, whereby multiple portions of the transducer module are configured to emit ultrasonic therapy at multiple acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude; and to apply ultrasonic therapy phase shifting, whereby the multiple portions of the transducer module are configured to emit ultrasonic therapy at multiple acoustic intensity phases, wherein the first phase is different from the second phase. In one embodiment, the multiple phases include discrete phase values. In one embodiment, the transducer module includes piezoelectric material, and the multiple portions of the transducer module are configured to generate multiple corresponding piezoelectric material changes in response to an electric field applied to the transducer module. In one embodiment, the multiple piezoelectric material changes include at least one of expansion and contraction of the material. In one embodiment, at least a portion of the transducer module is configured to emit ultrasonic therapy at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the transducer module varies over time. In one embodiment, the movement mechanism is configured to be programmable to provide variable spacing between a plurality of individual thermal cosmetic treatment zones. In one embodiment, the sequence of individual cosmetic treatment zones has a treatment spacing in the range of 1 mm to 25 mm. In one embodiment, the first and second switches include user-operated buttons or keys. In one embodiment, at least one of the first switch and the second switch is activated by a control module. In one embodiment, the ultrasonic treatment is at least one of a face lift, a brow lift, a chin lift, eye treatment, wrinkle reduction, scar reduction, burn treatment, tattoo removal, skin tightening, vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sun spot removal, fat treatment, cellulite treatment, shoulder treatment, vaginal rejuvenation, and acne treatment. In one embodiment, the transducer module is configured to provide ultrasonic treatment acoustic power in a range between 10 W and 1000 W and a frequency of 1 MHz to 20 MHz to thermally heat tissue to induce coagulation. In various embodiments, a treatment system for delivering simultaneous treatment at multiple depths includes a control device operable to control a sonication function for providing sonication treatment; and a handheld wand configured to direct the sonication treatment in a sequence of separate thermocosmetic treatment zones, the handheld wand including a transducer configured to apply the sonication treatment to tissue at locations within a focal depth, the locations being positioned within the thermocosmetic treatment zone, wherein the transducer is further configured to simultaneously apply the sonication treatment to tissue at multiple locations within the focal depth. In various embodiments, a method for performing a non-invasive cosmetic procedure on the skin by producing multiple simultaneous focal points at multiple depths with a single transducer includes coupling a transducer module to an ultrasound probe; wherein the ultrasound probe includes a first switch that controls acoustic imaging; wherein the ultrasound probe includes a second switch that controls acoustic therapy for causing multiple separate cosmetic treatment areas; wherein the ultrasound probe includes a movement mechanism that provides a desired spacing between the separate cosmetic treatment areas; bringing the transducer module into contact with the skin surface of a subject; activating the first switch on the ultrasound probe to acoustically image an area below the skin surface with the transducer module; and activating the second switch on the ultrasound probe to acoustically treat the area below the skin surface with the transducer module in a desired sequence of separate cosmetic treatment areas controlled by the movement mechanism, wherein the transducer module includes a single ultrasound transducer configured to apply ultrasound therapy to tissue at multiple focal depths. In various embodiments, an ultrasound treatment system for simultaneously generating multiple focal points at multiple depths in tissue using an ultrasound transducer includes a control device operable to control an ultrasound treatment function for providing ultrasound treatment; and a handheld wand configured to direct the ultrasound treatment in a sequence of separate thermal cosmetic treatment areas, the handheld wand including a transducer configured to apply ultrasound treatment to tissue at multiple locations at the focal depths. In various embodiments, an imaging and treatment system for cosmetic treatment at multiple depths in tissue includes an ultrasound probe configured for ultrasound imaging and ultrasound treatment of tissue at multiple focal depths, a transducer module configured to be coupled to the ultrasound probe, wherein the transducer module includes an ultrasound transducer configured to apply ultrasound treatment to tissue at multiple locations at the focal depths, a first switch operably controlling an ultrasound imaging function for providing ultrasound imaging, a second switch operably controlling an ultrasound treatment function for providing ultrasound treatment, and a movement mechanism configured to guide the ultrasound treatment in at least one sequence of separate thermal cosmetic treatment areas, and wherein the transducer module is configured to be operably coupled to at least one of the first switch, the second switch, and the movement mechanism; and a control module, wherein the control module includes a processor and a display for controlling the transducer module. In one embodiment, the plurality of locations are positioned within the cosmetic treatment area in a substantially linear sequence. In one embodiment, a first set of locations is positioned within the first cosmetic treatment area, and a second set of locations is positioned within the second cosmetic treatment area, the first area being different from the second area. In one embodiment, the first cosmetic treatment area comprises a substantially linear sequence of the first set of locations, and the second cosmetic treatment area comprises a substantially linear sequence of the second set of locations. In one embodiment, the transducer module is configured to apply ultrasound therapy using amplitude modulation, whereby the plurality of portions of the transducer module are configured to emit ultrasound therapy at a plurality of acoustic intensity amplitudes, wherein the first amplitude is different from the second amplitude. In one embodiment, the transducer module is configured to apply ultrasound therapy phase shifting, whereby the plurality of portions of the transducer module are configured to emit ultrasound therapy at a plurality of acoustic intensity phases, wherein the first phase is different from the second phase. In one embodiment, the transducer module is configured to apply ultrasound therapy using amplitude modulation, whereby the plurality of portions of the transducer module are configured to emit ultrasound therapy at a plurality of acoustic intensity amplitudes, wherein the first amplitude is different from the second amplitude; and apply ultrasound therapy phase shifting, whereby the plurality of portions of the transducer module are configured to emit ultrasound therapy at a plurality of acoustic intensity phases, wherein the first phase is different from the second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the transducer module comprises a piezoelectric material, and multiple portions of the transducer module are configured to generate a plurality of corresponding piezoelectric material changes in response to an electric field applied to the transducer module. In one embodiment, the plurality of piezoelectric material changes include at least one of expansion of the material and contraction of the material. In one embodiment, at least one portion of the transducer module is configured to emit ultrasonic therapeutic sound at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic therapeutic sound emitted by at least one portion of the transducer module varies over time. In one embodiment, the movement mechanism is configured to be programmed to provide variable spacing between a plurality of individual thermal cosmetic treatment zones. In one embodiment, the sequence of individual thermal cosmetic treatment zones has a treatment spacing in the range of 0.01 mm to 25 mm. In one embodiment, the first and second switches comprise user-operated buttons or keys. In one embodiment, at least one of the first and second switches is activated by a control module. In one embodiment, the therapeutic function is at least one of a face lift, a brow lift, a chin lift, eye treatment, wrinkle reduction, scar reduction, burn treatment, tattoo removal, skin tightening, vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sun spot removal, fat treatment, vaginal rejuvenation, and acne treatment. In one embodiment, the transducer module is configured to provide ultrasonic therapeutic acoustic power in a range between 10 W to 1000 W and a frequency of 1 MHz to 10 MHz to thermally heat tissue to induce coagulation. In various embodiments, a multi-focal ultrasound treatment system for simultaneous treatment at multiple depths includes a control device operable to control an ultrasound treatment function for providing ultrasound treatment; a handheld wand configured to direct the ultrasound treatment in a sequence of separate thermal cosmetic treatment zones, the handheld wand including a transducer configured to apply ultrasound treatment to tissue at locations within the focal depth, the locations being positioned within the thermal cosmetic treatment zone, wherein the transducer is further configured to simultaneously apply ultrasound treatment to tissue at multiple locations within the focal depth. In various embodiments, an imaging and simultaneous multifocal therapy system at multiple depths includes a module having an ultrasonic transducer, wherein the ultrasonic transducer is configured to apply ultrasonic therapy to tissue at multiple focal depths with at least one of the group consisting of amplitude modulated polarization and phase shifting, wherein the module further includes an interface guide designed to removably couple to a handheld wand to provide electronic communication and power between the module and the handheld wand. In one embodiment, the plurality of locations are positioned within the cosmetic treatment area in a substantially linear sequence. In one embodiment, a first set of locations is positioned within the first cosmetic treatment area, and a second set of locations is positioned within the second cosmetic treatment area, the first area being different from the second area. In one embodiment, the first cosmetic treatment area comprises a substantially linear sequence of the first set of locations, and the second cosmetic treatment area comprises a substantially linear sequence of the second set of locations. In one embodiment, the ultrasonic transducer is configured to apply the ultrasonic treatment using amplitude modulation, whereby the plurality of portions of the ultrasonic transducer are configured to emit the ultrasonic treatment at a plurality of acoustic intensity amplitudes, wherein the first amplitude is different from the second amplitude. In one embodiment, the ultrasonic transducer is configured to apply an ultrasonic treatment phase shift, whereby the plurality of portions of the ultrasonic transducer are configured to emit the ultrasonic treatment at a plurality of acoustic intensity phases, wherein the first phase is different from the second phase. In one embodiment, the ultrasonic transducer is configured to apply the ultrasonic treatment using amplitude modulation, whereby the plurality of portions of the ultrasonic transducer are configured to emit the ultrasonic treatment at a plurality of acoustic intensity amplitudes, wherein the first amplitude is different from the second amplitude; and to apply an ultrasonic treatment phase shift, whereby the plurality of portions of the ultrasonic transducer are configured to emit the ultrasonic treatment at a plurality of acoustic intensity phases, wherein the first phase is different from the second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the ultrasonic transducer comprises a piezoelectric material, and multiple portions of the ultrasonic transducer are configured to generate a plurality of corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer. In one embodiment, the plurality of piezoelectric material changes include at least one of expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, at least one portion of the ultrasonic transducer is configured to emit ultrasonic treatment at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic treatment emitted by at least one portion of the piezoelectric device varies over time. In one embodiment, the imaging and treatment system includes a motion mechanism that is programmed to provide spacing between a plurality of separate cosmetic treatment areas. In one embodiment, the sequence of separate cosmetic treatment areas has a treatment spacing in the range of 1 mm to 50 mm. In one embodiment, the ultrasonic treatment is at least one of a face lift, a brow lift, a chin lift, eye treatment, wrinkle reduction, scar reduction, burn treatment, tattoo removal, skin tightening, vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sun spot removal, fat treatment, vaginal rejuvenation, and acne treatment. In one embodiment, the ultrasonic transducer is configured to provide ultrasonic therapeutic acoustic power in the range of 1 W to 100 W and a frequency of 1 MHz to 10 MHz to thermally heat tissue to induce coagulation. In various embodiments, a treatment system for simultaneous treatment at multiple depths includes: a control device operable to control a sonication function for providing sonication treatment; and a handheld wand configured to direct the sonication treatment in a sequence of separate thermal cosmetic treatment areas, the handheld wand including a transducer configured to simultaneously apply the sonication treatment to tissue at multiple locations within the focal depth. In various embodiments, a non-invasive method for performing cosmetic procedures simultaneously at multiple depths, not performed by a physician, comprises coupling a transducer module to an ultrasound probe; wherein the transducer module comprises an ultrasound transducer configured to apply ultrasound treatment to tissue at multiple locations at a focal depth using at least one of the group consisting of amplitude-modulated polarization and phase shifting, wherein the ultrasound probe comprises a first switch that controls acoustic imaging; wherein the ultrasound probe comprises a second switch that controls the acoustic treatment for causing a plurality of separate cosmetic treatment areas; wherein the ultrasound probe comprises a movement mechanism that provides a desired spacing between the separate cosmetic treatment areas; bringing the transducer module into contact with a skin surface of a subject; activating the first switch on the ultrasound probe to acoustically image an area below the skin surface with the transducer module; and activating the second switch on the ultrasound probe to acoustically treat the area below the skin surface with the transducer module in a desired sequence of the separate cosmetic treatment areas controlled by the movement mechanism. In various embodiments, an ultrasound therapy system for dithering multiple simultaneous focal spots from an ultrasound transducer at multiple depths includes an ultrasound probe including an ultrasound transducer having a single transducer element adapted to simultaneously apply ultrasound therapy to tissue at multiple spaced focal depths, wherein the ultrasound transducer is polarized with at least a first polarization configuration and a second polarization configuration, and a control module coupled to the ultrasound probe for controlling the ultrasound transducer, wherein the control module modifies a spacing between spaced locations via dithering of the first and second focal regions such that a position of a beam focus is precisely moved at the spaced locations via the frequency-modulated dithering. In one embodiment, the plurality of locations are positioned within the cosmetic treatment area in a linear sequence, with the alternate locations separated by intervals that are dithered via frequency wobble. In one embodiment, a first set of locations are positioned within a first cosmetic treatment area, and a second set of locations are positioned within a second cosmetic treatment area, the first area being different from the second area. In one embodiment, the ultrasonic transducer is adapted to apply the ultrasonic treatment using amplitude modulation, whereby the plurality of portions of the ultrasonic transducer are adapted to emit the ultrasonic treatment at a plurality of acoustic intensity amplitudes, whereby the first amplitude is different from the second amplitude. In one embodiment, at least a portion of the ultrasonic transducer is adapted to emit the ultrasonic treatment at two or more acoustic intensity amplitudes, and whereby the amplitude of the ultrasonic treatment emitted by at least a portion of the piezoelectric element varies over time. In one embodiment, the ultrasonic transducer comprises a piezoelectric material, and the plurality of portions of the ultrasonic transducer are adapted to generate a plurality of corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer. In one embodiment, the plurality of piezoelectric material changes comprise at least one of expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, the ultrasonic transducer is adapted to apply the ultrasonic treatment via phase shifting, whereby the plurality of portions of the ultrasonic transducer are adapted to emit the ultrasonic treatment at a plurality of acoustic intensity phases, whereby the first phase is different from the second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the ultrasound transducer is adapted to apply ultrasound therapy using amplitude modulation, whereby the plurality of sections of the ultrasound transducer are adapted to emit ultrasound therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude; and the ultrasound therapy is applied, whereby the plurality of sections of the ultrasound transducer are adapted to emit ultrasound therapy at a plurality of acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the ultrasound therapy is at least one of: a face lift, a brow lift, a chin lift, eye treatment, wrinkle reduction, shoulder enhancement, buttock lift, scar reduction, burn treatment, skin tightening, vascular reduction, sweat gland treatment, sun spot removal, fat treatment, abdominal relaxation treatment, and cellulite treatment. In one embodiment, the ultrasound probe comprises a movement mechanism adapted to guide the ultrasound therapy in at least one pair of simultaneous sequences across separate thermal cosmetic treatment areas. In one embodiment, the ultrasound probe is configured for ultrasound imaging and ultrasound therapy. In one embodiment, the ultrasound probe comprises a transducer module adapted to apply the ultrasound therapy. In various embodiments, an ultrasound treatment system for dithering multiple simultaneous focal points at multiple depths from an ultrasound transducer during cosmetic treatment includes an ultrasound probe having a control module adapted to modify a separation between a first focal region and a second focal region via dithering, operable to control a switch for providing ultrasound treatment; and a movement mechanism adapted to direct the ultrasound treatment in at least a pair of simultaneous sequences of separate thermal cosmetic treatment zones; and a transducer module adapted to apply the ultrasound treatment, wherein the transducer module is adapted for ultrasound imaging and ultrasound treatment, wherein the transducer module is adapted to be coupled to the ultrasound probe, wherein the transducer module includes an ultrasound transducer adapted to apply the ultrasound treatment to tissue at multiple locations having at least two focal depths, wherein the transducer module is adapted to be operably coupled to at least one of the switch and the movement mechanism; and wherein the control module includes a processor and a display for controlling the transducer module. In one embodiment, the transducer module is adapted to apply ultrasonic therapy using amplitude modulation, whereby portions of the transducer module are adapted to transmit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the transducer module is adapted to apply ultrasonic therapy, whereby portions of the transducer module are adapted to transmit ultrasonic therapy at a plurality of acoustic intensity phases, wherein a first phase is different from a second phase. In various embodiments, a ultrasound therapy system for dithered simultaneous multi-focal therapy at multiple depths includes a module having an ultrasound transducer, wherein the ultrasound transducer is adapted to simultaneously apply ultrasound therapy to tissue at multiple intervals of depth in the tissue, wherein the module modifies the intervals between the multiple intervals of depth via dithering of a first focal region and a second focal region such that the position of the beam focus is precisely moved at the multiple intervals of depth via frequency-modulated dithering, wherein the module further includes an interface guide designed to removably couple to a handheld wand to provide electronic communication and power between the module and the handheld wand. In one embodiment, the ultrasonic transducer is adapted to apply ultrasonic therapy using amplitude modulation, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic therapy at multiple acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the ultrasonic transducer is adapted to apply ultrasonic therapy, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic therapy at multiple acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the ultrasonic transducer includes a piezoelectric material, and the multiple portions of the ultrasonic transducer are adapted to generate a plurality of corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer. In one embodiment, at least a portion of the ultrasonic transducer is adapted to emit ultrasonic therapy at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the ultrasonic transducer remains constant over time. In one embodiment, the ultrasound treatment is at least one of a face lift, a brow lift, a chin lift, an eye treatment, wrinkle reduction, shoulder enhancement, a butt lift, scar reduction, burn treatment, tattoo removal, skin tightening, vein removal, vein reduction, treating sweat glands, treating hyperhidrosis, sun spot removal, fat treatment, cellulite treatment, abdominal relaxation treatment, vaginal rejuvenation, and acne treatment. In various embodiments, a method for dithering a simultaneously focused ultrasound therapy beam at multiple depths includes providing an ultrasound probe including an ultrasound transducer comprising a single transducer element adapted to simultaneously apply ultrasound therapy to tissue at a plurality of spaced-apart locations at a plurality of focal depths, and a control module coupled to the ultrasound probe for controlling the ultrasound transducer and dithering the spacing between the spaced-apart locations of a first focal region and a second focal region via frequency modulation to move the position of the ultrasound focus at the spaced-apart locations. In one embodiment, the method further comprises imaging the first focal area with the ultrasonic imaging element. In one embodiment, the method further comprises imaging the second focal area with the ultrasonic imaging element. In one embodiment, the spacing between the first focal area and the second focal area is dithered within a range of 1-50%. In one embodiment, the spacing between the first focal area and the second focal area is 1.5 mm with a fluctuation of 0.1 mm. In one embodiment, the frequency modulation is within a range of 1-50%. In one embodiment, the ultrasonic treatment is at least one of a face lift, a brow lift, a chin lift, eye treatment, wrinkle reduction, shoulder enhancement, buttocks lift, scar reduction, burn treatment, tattoo removal, skin tightening, vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sun spot removal, fat treatment, vaginal rejuvenation, abdominal relaxation treatment, and acne treatment. In various embodiments, a method of simultaneously dithering a focused ultrasound beam at multiple depths includes providing an ultrasound probe including a single transducer element and a control module, wherein the single transducer element is adapted to apply ultrasound treatment to tissue at a focal region at a focal depth, wherein the control module is coupled to the ultrasound probe for controlling the single transducer element, and dithering the focal region via frequency modulation to vary a size of the focal region at the tissue. In one embodiment, the relative positions of the focal regions are jittered within a range of 1-50%. In one embodiment, the second focal region is simultaneously transmitted from a single transducer element. In one embodiment, the frequency modulation is within a range of 1-50%. In one embodiment, the system is designed to operate non-invasively to treat tissue. In one embodiment, the method operates in a non-invasive manner to treat tissue. In various embodiments, a sonic therapy system for delivering simultaneous multifocal therapy at multiple depths using an electrostrictor includes a module having a sonic transducer, wherein the sonic transducer is adapted to simultaneously apply sonic therapy to tissue at multiple intervals of depth in the tissue through application of the electrostrictor, wherein the module modifies the intervals between the multiple intervals of depth via dithering of a first focal region and a second focal region such that the position of the beam focus is precisely moved at the multiple intervals of depth via frequency-modulated dithering, wherein the module further includes an interface guide designed to removably couple to a handheld wand to provide electronic communication and power between the module and the handheld wand. In one embodiment, the ultrasonic transducer is adapted to apply ultrasonic therapy using amplitude modulation, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic therapy at multiple acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the ultrasonic transducer is adapted to apply ultrasonic therapy, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic therapy at multiple acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the ultrasonic transducer includes a piezoelectric material, and the multiple portions of the ultrasonic transducer are adapted to generate a plurality of corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer. In one embodiment, at least a portion of the ultrasonic transducer is adapted to emit ultrasonic therapy at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the ultrasonic transducer remains constant over time. In one embodiment, the ultrasound treatment is at least one of a face lift, a brow lift, a chin lift, an eye treatment, wrinkle reduction, shoulder enhancement, a butt lift, scar reduction, burn treatment, tattoo removal, skin tightening, vein removal, vein reduction, treating sweat glands, treating hyperhidrosis, sun spot removal, fat treatment, cellulite treatment, abdominal relaxation treatment, vaginal rejuvenation, and acne treatment. In various embodiments, an ultrasound therapy system is provided, having one or more of the features described in the specification. In various embodiments, a method of reducing imaging misalignment in a mobile ultrasound transducer is provided, having one or more of the features described in the specification. In various embodiments, an ultrasound therapy system for generating multiple simultaneous focal spots from an ultrasound transducer is provided, having one or more of the features described in the specification. In various embodiments, an ultrasound therapy system for delivering multi-focal therapy is provided, having one or more of the features described in the specification. In various embodiments, an ultrasound therapy module for forming multiple simultaneous focal areas from an ultrasound transducer in cosmetic treatments is provided, having one or more of the features described in the specification. In various embodiments, a method of generating a simultaneously focused ultrasound therapy beam using multi-channel signal mixing is provided, having one or more of the features described in the specification. In various embodiments, a method of generating a simultaneously focused ultrasound beam is provided, having one or more of the features described in the specification. In several embodiments described herein, the procedures are purely cosmetic rather than medical. For example, in one embodiment, the methods described herein need not be performed by a doctor, but rather at a spa or other beauty facility. In some embodiments, the system can be used for non-invasive cosmetic treatments of the skin. The methods outlined above and further elaborated below describe certain actions taken by a practitioner; however, it should be understood that they may also include instructions for such actions by another party. Thus, an action such as "dithering the energy beam" includes "instructing dithering of the energy beam." In some embodiments, the system includes various features that exist as a single feature (as opposed to a plurality of features). For example, in one embodiment, the system includes a single transducer element that produces two simultaneous therapeutic foci of dithering. In alternative embodiments, multiple features or components are provided. In various embodiments, the system comprises, consists essentially of, or consists of one, two, three, or more embodiments of any feature or component disclosed herein. In some embodiments, a feature or component is not included and may be negatively disclaimed from a particular claim, such that the system lacks such a feature or component. Furthermore, further areas of applicability will become apparent from the description provided herein.It should be understood that the description and specific examples are intended for purposes of illustration only and are not intended to limit the scope of the embodiments disclosed herein. The following description illustrates examples of embodiments and is not intended to limit the invention or its teachings, applications, or uses. It should be understood that throughout the drawings, corresponding reference numerals indicate identical or corresponding parts and features. The descriptions of specific embodiments indicated in the various embodiments of the invention are for illustrative purposes only and are not intended to limit the scope of the invention disclosed herein. Furthermore, the recitation of multiple embodiments having described features is not intended to exclude other embodiments having additional features or other embodiments incorporating different combinations of the described features. Furthermore, features from one embodiment (e.g., in one figure) may be combined with the descriptions (and figures) of other embodiments. In various embodiments, systems and methods for ultrasonic treatment of tissue are adapted and / or configured to provide cosmetic treatments. In some embodiments, several embodiments provide devices and methods that direct ultrasonic treatment to a single focal point or multiple simultaneous focal points, employing ultrasonic imaging to confirm adequate acoustic coupling to the treatment area to improve performance or provide improved correlation between movement in the first and second directions when imaging cosmetic and / or medical procedures. As used herein, "simultaneously" refers to occurring simultaneously or with a time difference of less than 1 ms, 0.5 ms, 0.1 ms, 0.05 ms, or 0.01 ms. In various embodiments, ultrasonic energy is used to non-invasively treat tissue below or even at the surface of the skin, such as the epidermis, dermis, fascia, muscle, fat, and the superficial musculoaponeurotic system ("SMAS"). The ultrasonic energy can be focused to one or more treatment points and / or areas, can be unfocused and / or defocused, and can be applied to a region of interest comprising at least one of the epidermis, dermis, subdermis, fascia, muscle, fat, cellulite, and SMAS to achieve cosmetic and / or therapeutic effects. In various embodiments, the systems and / or methods provide non-invasive skin treatments to tissues through thermal treatment, coagulation, ablation, and / or tightening. In several embodiments disclosed herein, non-invasive ultrasound is used to achieve one or more of the following: face lift, brow lift, chin lift, eye treatment (e.g., cheekbone bags, treatment of infraorbital laxity), wrinkle reduction, fat reduction (e.g., treatment of fat and / or cellulite), cellulite treatment (e.g., in female lipodystrophy with or without recessed lipodystrophy), shoulder enhancement (e.g., upper chest), buttock lift (e.g., buttock tightening), skin laxity treatment (e.g., treating tissue for tightening or abdominal laxity treatment), scar reduction, burn treatment, tattoo removal, vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sun spot removal, acne treatment, and pimple removal. In one embodiment, fat reduction is achieved. In various embodiments, one or more characteristics of cellulite (e.g., dimpling or non-dimpling female lipodystrophy) (e.g., compared to untreated tissue) (e.g., pitting, nodules, "orange peel" appearance, etc.) are reduced or improved by about 10-20%, 20-40%, 40-60%, 60-80%, or more (and overlapping ranges therein). In one embodiment, the shoulders are treated. In some embodiments, two, three, or more beneficial effects are achieved during the same treatment session and can be achieved simultaneously. Various embodiments of the present invention relate to devices or methods for controlling the delivery of energy to tissue. In various embodiments, the various forms of energy may include acoustic, ultrasonic, light, laser, radiofrequency (RF), microwave, electromagnetic, radiation, thermal, cryogenic, electron beam, photon-based, magnetic, magnetic resonance, and / or other energy forms. Various embodiments of the present invention relate to devices or methods for splitting an ultrasonic energy beam into multiple beams. In various embodiments, the devices or methods can be used to modify the delivery of ultrasonic acoustic energy in any procedure, such as, but not limited to, therapeutic ultrasound, diagnostic ultrasound, ultrasonic welding, any application involving the coupling of mechanical waves to an object, and other procedures. Typically, therapeutic ultrasound achieves tissue effects by concentrating acoustic energy from an aperture using focusing techniques. In some cases, high-intensity focused ultrasound (HIFU) is used in this manner for therapeutic purposes. In one embodiment, the tissue effect produced by applying therapeutic ultrasound at a specific depth may be referred to as the generation of a thermal coagulation point (TCP). In some embodiments, the region may comprise a point. In some embodiments, the region is a line, plane, sphere, ellipse, cube, or other one-, two-, or three-dimensional shape. By generating TCP at a specific location, thermal and / or mechanical ablation of tissue can occur non-invasively or remotely. In some embodiments, the ultrasound treatment does not include cavitation and / or shock waves. In some embodiments, the ultrasound treatment includes cavitation and / or shock waves. In one embodiment, the TCPs can be generated in a linear or substantially linear, curved or substantially curved region or sequence, wherein each individual TCP is separated from an adjacent TCP by a treatment interval. In one embodiment, multiple TCP sequences can be generated within the treatment region. For example, TCPs can be formed along a first sequence and a second sequence separated from the first sequence by a treatment distance. Although therapeutic ultrasound therapy can be administered by generating individual TCPs in one or more sequences of individual TCPs, it may be desirable to reduce treatment time and the corresponding risk of pain and / or discomfort experienced by the patient. Treatment time can be reduced by generating multiple TCPs simultaneously, nearly simultaneously, or sequentially. In some embodiments, generating multiple TCPs can reduce treatment time by 10%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, 80%, or more. Various embodiments of the present invention address potential challenges associated with administering ultrasound therapy. In various embodiments, the time required to achieve desired cosmetic and / or therapeutic treatments at target tissues is reduced. In various embodiments, the target tissue is, but is not limited to, any of the following: skin, eyelids, eyelashes, eyebrows, tear ducts, crow's feet, wrinkles, eyes, nose, mouth (e.g., nasolabial folds, perioral wrinkles), tongue, teeth, gums, ears, brain, heart, lungs, ribs, abdomen (e.g., for abdominal relaxation), stomach, liver, kidneys, uterus, breasts, vagina, prostate, testicles, glands, thyroid gland, internal organs, hair, muscle, bone, ligament, cartilage, fat, fat lobes, adipose tissue, subcutaneous tissue, implanted tissue, implanted organ, lymph, tumor, cyst, abscess, or part of a nerve, or any combination thereof. Various embodiments of simultaneous ultrasound treatment at multiple locations in tissue are described in U.S. Application No. 14 / 193,234, published on September 11, 2014 as U.S. Publication No. 2014 / 0257145, which is incorporated herein by reference in its entirety. System Overview Referring to Figures 1A, 1B, and 1C, various embodiments of an ultrasound system 20 include a handheld wand (e.g., a handpiece) 100, a module (e.g., a transducer module, a cartridge, a probe) 200, and a controller (e.g., a console) 300. In some embodiments, the console 300 includes a communication system (e.g., Wi-Fi, Bluetooth, a modem, etc.) for communicating with other parties, manufacturers, suppliers, service providers, the internet, and / or the cloud. In some embodiments, a cart 301 provides mobility and / or location for the system 20 and may include wheels, a surface for writing on or placing components, and / or compartments 302 (e.g., drawers, containers, shelves, etc.) for storing or organizing components. In some embodiments, the cart includes a power source, such as a power connection to a battery and / or one or more wires for connecting power and communications (e.g., Ethernet) to the system 20. In some embodiments, the system 20 includes the cart 301. In some embodiments, the system 20 does not include the cart 301. The handheld wand 100 can be coupled to the controller 300 via an interface 130, which can be wired or wireless. The interface 130 can be coupled to the handheld wand 100 via a connector 145. The distal end of the interface 130 can be connected to a controller connector on a circuit 345 (not shown). In one embodiment, the interface 130 can transmit controllable power from the controller 300 to the handheld wand 100. In one embodiment, the system 20 has multiple imaging channels (e.g., 8 channels) for ultra-clear HD (high-definition) visualization of subcutaneous structures for improved imaging. In one embodiment, the system 20 includes multiple treatment channels (e.g., 8 channels) and precision linear drive motors, which double treatment accuracy while increasing speed (e.g., by 25%, 40%, 50%, 60%, 75%, 100%, or more). Together, these features establish one of the industry's most versatile system platforms and lay the foundation for unprecedented future possibilities. In various embodiments, the controller 300 can be adapted and / or configured to operate with the handheld wand 100 and module 200, as well as the functionality of the entire ultrasound system 20. In various embodiments, multiple controllers 300, 300', 300", etc. can be adapted and / or configured to operate with multiple handheld wands 100, 100', 100", etc. and / or multiple modules 200, 200', 200", etc. The controller 300 can include connectivity to one or more interactive graphical displays 310, which can include touchscreen monitors and graphical user interfaces (GUIs) that allow users to interact with the ultrasound system 20. In one embodiment, a second, smaller, more mobile display allows users to more easily locate and view the treatment screen. In one embodiment, the second display allows system users to view the treatment screen (e.g., on a wall, on a mobile device, on a large screen, or on a remote screen). In one embodiment, the graphical display 310 includes a touchscreen interface 315 (not shown). In various embodiments, the display 310 sets and displays operating conditions, including device activation status, treatment parameters, system messages and prompts, and ultrasound images. In various embodiments, the controller 300 can be adapted and / or configured to include, for example, a microprocessor with software and input / output devices, systems and devices for controlling electronic and / or mechanical scanning and / or transducer multiplexing and / or multiplexing of transducer modules, systems for power delivery, systems for monitoring, systems for sensing the spatial position of the probe and / or transducer and / or multiplexing of transducer modules, and / or systems for processing user input and recording treatment results, etc. In various embodiments, the controller 300 can include a system processor and various analog and / or digital control logic, such as one or more of a microcontroller, a microprocessor, a field programmable gate array, a computer board, and related components, including firmware and control software, which can be capable of interfacing with user controls and interface circuitry, as well as input / output circuitry and system interfaces for communication, display, interfacing, storage, documentation, and other useful functions. The system software running on the system process can be adapted and / or configured to control all initialization, timing, level setting, monitoring, safety monitoring, and all other ultrasound system functions used to achieve user-defined treatment goals. In addition, the controller 300 may include various input / output modules, such as switches, buttons, etc., which can also be appropriately adapted and / or configured to control the operation of the ultrasound system 20. In one embodiment, the handheld wand 100 includes one or more finger-activated controls or switches, such as 150 and 160. In various embodiments, one or more thermal treatment controls 160 (e.g., switches, buttons) start and / or stop treatment. In various embodiments, one or more imaging controls 150 (e.g., switches, buttons) start and / or stop imaging. In one embodiment, the handheld wand 100 may include a removable module 200. In other embodiments, the module 200 may not be removable. In various embodiments, the module 200 may be mechanically coupled to the handheld wand 100 using a latch or coupler 140. In various embodiments, an interface guide 235 or multiple interface guides 235 may be used to facilitate coupling the module 200 to the handheld wand 100. The module 200 may include one or more ultrasonic transducers 280. In some embodiments, the ultrasonic transducer 280 includes one or more ultrasonic elements. The module 200 may include one or more ultrasonic elements. The handheld wand 100 can include an imaging-only module, a therapy-only module, an imaging and therapy module, and the like. In various embodiments, the ultrasonic transducer 280 is movable within the module 200 in one or more directions 290. The transducer 280 is connected to a motion mechanism 400 (also referred to as a movement mechanism). In various embodiments, the motion mechanism includes zero or one bearings, shafts, rods, screws, lead screws 401, an encoder 402 (e.g., an optical encoder that measures the position of the transducer 280), and a motor 403 (e.g., a stepper motor) to help ensure accurate and repeatable movement of the transducer 280 within the module 200. In various embodiments, the module 200 can include the transducer 280, which can transmit energy through the acoustically transparent member 230. In one embodiment, the controller 300 can be coupled to the handheld wand 100 via the interface 130, and the graphical user interface 310 can be adapted and / or configured for controlling the module 200. In one embodiment, the controller 300 can provide power to the handheld wand 100. In one embodiment, the handheld wand 100 can include a power source. In one embodiment, the switch 150 can be adapted and / or configured to control a tissue imaging function, and the switch 160 can be adapted and / or configured to control a tissue treatment function. In various embodiments, the module 200, through controlled operation of the controller 300 of the transducer 280, provides for delivery of the transmitted energy 50 at an appropriate focal depth, distribution, timing, and energy level to achieve a desired therapeutic effect with a thermal coagulation zone 550 ("TCP," e.g., thermal coagulation point). In one embodiment, the module 200 can be coupled to the handheld wand 100. The module 200 can transmit and receive energy, such as ultrasonic energy. The module 200 can be electronically coupled to the handheld wand 100, and such coupling can include an interface for communicating with the controller 300. In one embodiment, the interface guide 235 can be adapted and / or configured to provide electronic communication between the module 200 and the handheld wand 100. The module 200 can include various probe and / or transducer configurations. For example, the module 200 can be adapted and / or configured for a combined dual-mode imaging / therapy transducer, coupled or co-housed imaging / therapy transducers, independent therapy and imaging probes, etc. In one embodiment, when the module 200 is inserted into or connected to the handheld wand 100, the controller 300 automatically detects it and updates the interactive graphical display 310. In some embodiments, an access key 320 (e.g., a secure USB drive or key) is connected (e.g., removably) to system 20 to enable system 20 operation. In various embodiments, the access key is programmed to be client-specific and serves a variety of functions, including system security, country / region-specific access to treatment guidelines and features, software upgrades, support log transfer, and / or credit transfer and / or storage. In various embodiments, system 20 has internet and / or data connectivity. In some embodiments, this connectivity provides a method for transferring data between the system 20 provider and the client. In various embodiments, this data includes credit, software updates, and support logs. Connectivity is categorized into different models depending on how the user console connects to the internet. In one embodiment, disconnected model connectivity includes the console disconnected from the internet and the client unable to access the internet. Credit transfer and software upgrades are performed by sending the access key (e.g., a USB drive) to the client. In one embodiment, semi-connected model connectivity includes the console disconnected from the internet, but the client still has internet access. Credit transfers, software upgrades, and support log transfers are performed using the client's personal computer, smartphone, or other computing device in conjunction with system access key data transfer. In one embodiment, fully connected connectivity includes a console wirelessly connected to the internet using Wi-Fi, a cellular modem, Bluetooth, or other protocols. Credit transfers, software upgrades, and support log transfers occur directly between the console and the cloud. In various embodiments, system 20 connects to an online portal for streamlined inventory management, on-demand purchasing, and business analytics insights to take a client's beauty treatment business to the next level. In various embodiments, ultrasound energy is used to non-invasively treat tissue beneath or even at the skin's surface, such as the epidermis, dermis, hypodermis, fascia, and superficial musculoaponeurotic system (SMAS), and / or muscle. The tissue may also include blood vessels and / or nerves. The ultrasound energy may be focused, unfocused, or defocused and applied to a region of interest comprising at least one of the epidermis, dermis, hypodermis, fascia, and SMAS to achieve a therapeutic effect. FIG2 is a schematic diagram of an ultrasound system 20 coupled to a region of interest 10. In various embodiments, the tissue layers of region of interest 10 may be located anywhere on a subject's body. In one embodiment, the tissue layers are located in the head and facial region of a subject. A cross-sectional view of the tissue of region of interest 10 includes skin surface 501, epidermis 502, dermis 503, fat layer 505, superficial musculoaponeurotic system 507 (hereinafter referred to as "SMAS 507"), and muscle layer 509. The tissue may also include hypodermis 504, which may include any tissue beneath dermis 503. The combination of these layers can be collectively referred to as subcutaneous tissue 510. Also shown in FIG. 2 is a treatment area 525 located beneath surface 501. In one embodiment, surface 501 can be the skin surface of subject 500. While embodiments involving treatment at the tissue layer may be used as examples herein, the system can be applied to any tissue in the body. In various embodiments, the system and / or method can be used on tissue (including, but not limited to, muscle, fascia, SMAS, dermis, epidermis, fat, adipocytes, cellulite (which may be referred to as female lipodystrophy (e.g., non-depressing female lipodystrophy), collagen, skin, and blood vessels) on the face, neck, head, arms, legs, or any other location on or within the body (including body cavities). In various embodiments, cellulite (e.g., non-depressing female lipodystrophy) is reduced by 2%, 5%, 10%, 15%, 20%, 25%, 30%, 40%, 50%, 75%, 80%, 90%, 95%, or any range thereof. 2 , an embodiment of an ultrasound system 20 includes a handheld wand 100, a module 200, and a controller 300. In one embodiment, the module 200 includes a transducer 280. FIG3 illustrates an embodiment of the ultrasound system 20 having a transducer 280 adapted and / or configured to treat tissue at multiple focal depths 278. In one embodiment, the focal depth 278 is the distance between the transducer 280 and the target tissue for treatment. In one embodiment, the focal depth 278 is fixed for a given transducer 280. In one embodiment, the focal depth 278 is variable for a given transducer 280. In one embodiment, the transducer 280 is configured to simultaneously treat at multiple depths below the skin surface (e.g., 1.5 mm, 3.0 mm, 4.5 mm, or other depths). 4 , module 200 may include a transducer 280 that transmits energy through acoustically transparent member 230. In various embodiments, depth may refer to depth of focus 278. In one embodiment, transducer 280 may have an offset distance 270, which is the distance between transducer 280 and the surface of acoustically transparent member 230. In one embodiment, depth of focus 278 of transducer 280 is a fixed distance from the transducer. In one embodiment, transducer 280 may have a fixed offset distance 270 from the transducer to acoustically transparent member 230. In one embodiment, acoustically transparent member 230 is adapted and / or configured to be located at a position on module 200 or ultrasound system 20 to contact skin surface 501. In various embodiments, the amount by which depth of focus 278 exceeds offset distance 270 corresponds to treatment of a target area at a tissue depth 279 below skin surface 501. In various embodiments, when the ultrasound system 20 is placed in physical contact with the skin surface 501, the tissue depth 279 is the distance between the acoustically transparent member 230 and the target area, measured as the distance from the portion of the handheld wand 100 or module 200 surface contacting the skin (with or without acoustic coupling gel, medium, etc.) and the depth in the tissue of the target area from that point of contact. In one embodiment, the depth of focus 278 may correspond to the sum of the offset distance 270 (measured from the surface of the acoustically transparent member 230 in contact with the coupling medium and / or skin 501) plus the tissue depth 279 below the skin surface 501 to the target area. In various embodiments, the acoustically transparent member 230 is not used. The coupling components can include various substances, materials, and / or devices to facilitate coupling of the transducer 280 or module 200 to the region of interest. For example, the coupling components can include an acoustic coupling system adapted and / or configured for acoustic coupling of ultrasonic energy and signals. The acoustic coupling system, with possible connections (e.g., manifolds), can be used to couple sound into the region of interest, providing liquid or fluid-filled lens focusing. The coupling system can facilitate such coupling by using one or more coupling media, including air, gas, water, liquid, fluid, gel, solid, non-gel, and / or any combination thereof, or any other medium that allows for signal transmission between the transducer 280 and the region of interest. In one embodiment, the one or more coupling media are provided internally to the transducer. In one embodiment, the fluid-filled module 200 contains the one or more coupling media within a housing. In one embodiment, the fluid-filled module 200 contains the one or more coupling media within a sealed housing that is separable from the dry portion of the ultrasonic device. In various embodiments, the coupling medium is used to transmit ultrasonic energy between one or more devices and tissue with a transmission efficiency of 100%, 99% or greater, 98% or greater, 95% or greater, 90% or greater, 80% or greater, 75% or greater, 60% or greater, 50% or greater, 40% or greater, 30% or greater, 25% or greater, 20% or greater, 10% or greater and / or 5% or greater. In various embodiments, the transducer 280 can image and treat the region of interest at any suitable tissue depth 279. In one embodiment, the transducer 280 can provide acoustic power in a range of approximately 1 W or less, between approximately 1 W and approximately 100 W, and greater than approximately 100 W (e.g., 200 W, 300 W, 400 W, 500 W). In one embodiment, the transducer 280 can provide acoustic power at frequencies of approximately 1 MHz or less, between approximately 1 MHz and approximately 10 MHz (e.g., 3 MHz, 4 MHz, 4.5 MHz, 7 MHz, 10 MHz), and greater than approximately 10 MHz. In one embodiment, the module 200 has a depth of focus 278 for treating at a tissue depth 279 of approximately 4.5 mm below the skin surface 501. In one embodiment, the module 200 has a depth of focus 278 for treating at a tissue depth 279 of approximately 3 mm below the skin surface 501. In one embodiment, the module 200 has a focal depth 278 for treating at a tissue depth 279 of approximately 1.5 mm below the skin surface 501. Non-limiting embodiments of the transducer 280 or module 200 can be adapted and / or configured to deliver ultrasonic energy at a tissue depth of 1.5 mm, 3 mm, 4.5 mm, 6 mm, 7 mm, less than 3 mm, between 3 mm and 4.5 mm, between 4.5 mm and 6 mm, greater than 4.5 mm, greater than 6 mm, etc., and any point within the ranges of 0-3 mm, 0-4.5 mm, 0-6 mm, 0-25 mm, 0-100 mm, etc., and any depth therein. In one embodiment, the ultrasonic system 20 is provided with two or more transducers 280. For example, a first transducer module may apply therapy at a first tissue depth (e.g., approximately 4.5 mm), a second transducer module may apply therapy at a second tissue depth (e.g., approximately 3 mm), and a third transducer module may apply therapy at a third tissue depth (e.g., approximately 1.5-2 mm). In one embodiment, at least some or all of the transducer modules may be adapted and / or configured to apply therapy at approximately the same depth. In various embodiments, varying the number of focal locations (e.g., with tissue depths 279 ) used for ultrasound procedures can be advantageous because it allows the patient to be treated at different tissue depths, even if the focal depth 278 of the transducer 280 is fixed. This can provide synergistic results and maximize the clinical outcome of a single treatment session. For example, treatment at multiple depths beneath a single surface area allows for a greater total volume of tissue treatment, resulting in enhanced collagen formation and tightening. Furthermore, treatment at different depths affects different types of tissue, thereby producing different clinical effects that, together, provide an enhanced overall cosmetic outcome. For example, superficial treatment can reduce the visibility of wrinkles, while deeper treatment can induce the formation of more collagen growth. Similarly, treatment at various locations, at the same or different depths, can improve treatment outcomes. While treating a subject at different locations during a single treatment session may be advantageous in some embodiments, in other embodiments, sequential treatments may be beneficial over time. For example, a subject may be treated at a first depth at a first time, at a second depth at a second time, and so on. In various embodiments, the time period may be on the order of nanoseconds, microseconds, milliseconds, seconds, minutes, hours, days, weeks, months, or other time periods. New collagen generated by a first treatment may be more sensitive to subsequent treatments, which may be desirable for some indications. Alternatively, performing multiple treatment depths over the same surface area during a single treatment session may be advantageous because treatment at one depth may synergistically enhance or complement treatment at another depth (due to, for example, enhanced blood flow, stimulation of growth factors, hormone stimulation, etc.). In several embodiments, different transducer modules provide treatment at different depths. In one embodiment, a single transducer module can be adjusted or controlled for varying depths. Safety features that minimize the risk of selecting the wrong depth can be used in conjunction with a single module system. In several embodiments, a method for treating the lower face and neck region (e.g., the submental area) is provided. In several embodiments, a method for treating (e.g., softening) chin-lip folds is provided. In other embodiments, a method for treating the eye area (e.g., zygomatic bags, treating infraorbital laxity) is provided. By treating at variable depths, several embodiments achieve improved upper eyelid laxity and periorbital lines and texture. By treating at different locations in a single session, optimal clinical results (e.g., softening, tightening) can be achieved. In several embodiments, the treatment methods described herein are non-invasive cosmetic procedures. In some embodiments, the methods can be used in conjunction with invasive procedures, such as surgical facelifts or liposuction, where skin tightening is desired. In various embodiments, the methods can be applied to any area of ​​the body. In one embodiment, the transducer module 200 enables treatment sequences at fixed depths at or below the skin surface. In one embodiment, the transducer module enables treatment sequences at one, two, or more variable or fixed depths below the dermis. In several embodiments, the transducer module includes a movement mechanism adapted and / or configured to direct ultrasound treatments in a sequence of individual thermal lesions (hereinafter referred to as "thermal coagulation points" or "TCPs") at a fixed focal depth. In one embodiment, the sequence of individual TCPs has a treatment interval within a range of approximately 0.01 mm to approximately 25 mm (e.g., 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 5 mm, 10 mm, 20 mm, and any range thereof), with the intervals being dithered by 1-50% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any range thereof). For example, the spacing can be 1.1 mm or less, 1.5 mm or more, between about 1.1 mm and about 1.5 mm, etc. In one embodiment, the individual TCPs are discrete. In one embodiment, the individual TCPs overlap. In one embodiment, the movement mechanism is adapted and / or configured to be programmed to provide variable spacing between the individual TCPs. In one embodiment, the dithering can be adapted and / or configured to provide variable spacing between the individual TCPs. In several embodiments, the transducer module includes a movement mechanism adapted and / or configured to direct the ultrasound treatment in a sequence such that the TCPs are formed in a linear or substantially linear sequence separated by a treatment distance. For example, the transducer module can be adapted and / or configured to form TCPs along a first linear sequence and a second linear sequence separated from the first linear sequence by a treatment distance. In one embodiment, the treatment distance between adjacent linear sequences of individual TCPs is in the range of about 0.01 mm to about 25 mm. In one embodiment, the treatment distance between adjacent linear sequences of individual TCPs is about 0.01 mm to about 50 mm. For example, the treatment distance can be 2 mm or less, 3 mm or more, between about 2 mm and about 3 mm, etc. In several embodiments, the transducer module may include one or more motion mechanisms 400 adapted and / or configured to direct ultrasound therapy in a sequence such that TCPs are formed in a linear or substantially linear sequence of individual thermal lesions separated by a treatment distance from other linear sequences. In one embodiment, therapy is applied in a first direction 290 (e.g., push). In one embodiment, therapy is applied opposite to the first direction 290 (e.g., pull). In one embodiment, therapy is applied in both the first direction 290 and the direction opposite to the first direction (e.g., push and pull). In one embodiment, the treatment distance separating the linear or substantially linear TCP sequences is the same or substantially the same.In one embodiment, the treatment distance separating the linear or substantially linear TCP sequences is different or substantially different for various adjacent pairs of linear TCP sequences. In one embodiment, first and second removable transducer modules are provided. In one embodiment, each of the first and second transducer modules is adapted and / or configured for both ultrasound imaging and ultrasound therapy. In one embodiment, the transducer module is adapted and / or configured for therapy only. In one embodiment, the imaging transducer can be attached to a handle or handheld wand of the probe. The first and second transducer modules are adapted and / or configured for interchangeable coupling to the handheld wand. The first transducer module is adapted and / or configured to apply ultrasound therapy to a first tissue layer, while the second transducer module is adapted and / or configured to apply ultrasound therapy to a second tissue layer. The second layer of tissue is at a different depth than the first layer of tissue. As shown in FIG3 , in various embodiments, the module 200, through controlled operation of the controller 300, provides for delivering the emitted energy 50 at an appropriate focal depth 278, distribution, timing, and energy level to achieve the desired therapeutic effect of controlled thermal injury to treat at least one of the epidermis 502, dermis 503, fat 505, SMAS 507, muscle 509, and / or hypodermis 504. FIG3 illustrates one embodiment of a depth corresponding to a depth for treating muscle. In various embodiments, the depth can correspond to any tissue, tissue layer, skin, epidermis, dermis, hypodermis, fat, SMAS, muscle, blood vessels, nerves, or other tissue. During operation, the module 200 and / or transducer 280 can also be mechanically and / or electronically scanned along the surface 501 to treat an extended area. Before, during, and after delivery of ultrasonic energy 50 to at least one of the epidermis 502, dermis 503, hypodermis 504, fat layer 505, SMAS layer 507, and / or muscle layer 509, monitoring of the treatment area and surrounding structures may be provided to plan and evaluate results and / or provide feedback to the controller 300 and the user via the graphical interface 310. In one embodiment, the ultrasonic system 20 generates ultrasonic energy that is directed and focused beneath a surface 501. This controlled and focused ultrasonic energy 50 creates thermal coagulation points or zones (TCPs) 550. In one embodiment, the ultrasonic energy 50 creates voids in the subcutaneous tissue 510. In various embodiments, the emitted energy 50 targets tissue beneath the surface 501, cutting, ablating, coagulating, micro-ablating, manipulating, and / or inducing TCPs 550 in the tissue portion 10 beneath the surface 501 at a specified focal depth 278. In one embodiment, during a treatment sequence, the transducer 280 moves in the directions indicated by arrows labeled 290 at specified intervals 295 to create a series of treatment zones 254, each receiving emitted energy 50 to create one or more TCPs 550. In one embodiment, the arrow labeled 291 illustrates an axis or direction orthogonal or parallel to arrow 290, and the spacing of the TCPs 550 illustrates that the TCPs can be spaced orthogonal or parallel to the direction of motion of the transducer 280. In some embodiments, the orientation of the spaced TCPs can be set at any angle from 0-180 degrees to arrow 290. In some embodiments, the orientation of the spaced TCPs can be set at any angle from 0-180 degrees based on the orientation of the polarization regions on transducer 280. In various embodiments, the transducer module can include one or more transducer elements. The transducer elements can include a piezoelectrically active material, such as lead zirconate titanate (PZT), or any other piezoelectrically active material, such as piezoelectric ceramics, crystals, plastics, and / or composites, as well as lithium niobate, lead titanate, barium titanate, and / or lead metaniobate. In various embodiments, in addition to or in lieu of the piezoelectrically active material, the transducer module can include any other material suitable and / or configured for generating radiation and / or acoustic energy. In various embodiments, the transducer module can be adapted and / or configured to operate at different frequencies and treatment depths. Transducer properties can be determined by outer diameter ("OD") and focal length (F). L ) is defined. In one embodiment, the transducer may be adapted and / or configured to have an OD = 19 mm and an F L = 15mm. In other embodiments, other suitable OD and F L Values, such as OD less than about 19 mm, greater than about 19 mm, etc., F LLess than about 15 mm, greater than about 15 mm, etc. The transducer module can be adapted and / or configured to apply ultrasonic energy at different target tissue depths. As described above, in some embodiments, the transducer module includes a moving mechanism that is adapted and / or configured to guide ultrasonic treatment in a linear or substantially linear sequence of individual TCPs with treatment intervals between the individual TCPs. For example, the treatment intervals can be approximately 1.1 mm, 1.5 mm, etc. In some embodiments, the transducer module can also include a moving mechanism that is adapted and / or configured to guide ultrasonic treatment in a sequence such that TCPs are formed in a linear or substantially linear sequence separated by treatment intervals. For example, the transducer module can be adapted and / or configured to form TCPs along a first linear sequence and a second linear sequence separated from the first linear sequence by a treatment interval of between about 2 mm and 3 mm. In one embodiment, the user can manually move the transducer module on the surface of the treatment area to produce adjacent linear sequences of TCPs. In one embodiment, the moving mechanism can automatically move the transducer module on the surface of the treatment area to produce adjacent linear sequences of TCPs. Aperture Space Frequency Analysis and Fourier Transform In various embodiments, spatial frequency analysis techniques based on Fourier analysis and Fourier optics can be used to improve the efficiency of therapeutic treatment. The system h(t) is stimulated by When x(t) is excited, the input x(t) and output The relationship between y(t) is related by the following convolution function: (1) In various embodiments, a Fourier transform may be applied to calculate the convolution of Equation (1). The continuous one-dimensional Fourier transform may be defined as: (2) Here f is frequency and t is time. It can be shown that convolution in the time domain is equivalent to multiplication in the frequency domain: (3) In various embodiments, the Fraunhofer approximation can be used to derive the relationship between the transducer opening or aperture and the resulting ultrasonic beam response. The Fraunhofer approximation was derived in Joseph Goodman, The far-field composite amplitude pattern generated by a composite aperture is described in "Introduction to Fourier Optics" (3rd edition, 2004), the entire contents of which are incorporated herein by reference. According to the Fraunhofer approximation, the far-field composite amplitude pattern generated by a composite aperture is equal to the two-dimensional Fourier transform of the aperture amplitude and phase. In several embodiments, this relationship in optics can be extended to ultrasonics, as linear wave equations can be used to represent the propagation of light and sound. In the case of optics and / or ultrasonics, the two-dimensional Fourier transform can determine the acoustic wave pressure amplitude distribution at the focus of the transducer. For focusing systems, a variable representing depth z can be used to represent the focal length z f replace. (4a) (4b) In various embodiments, Fourier optics and Fourier transform identities (some of which are listed in Table 1 below) can be applied to ultrasonic transducers to determine the intensity distribution corresponding to the transducer design. The Fourier transform of rect(ax) is the sinc function. As another example, the Fourier transform of a two-dimensional circle of uniform amplitude is a first-order Bessel function, which can be expressed as J 1 . Table 1 In some embodiments, the ultrasonic transducer can have a rectangular aperture of suitable size and focal length. In some embodiments, the ultrasonic transducer can have a circular aperture of suitable size and focal length. In one embodiment, the transducer can have a circular aperture with an outer radius of approximately 9.5 mm, an inner diameter of approximately 2 mm, and a focal length of approximately 15 mm. The aperture of a circular transducer can be described as: (5a) (5b) For example, in one embodiment, variable "a" may be approximately 9.5 mm and variable "b" in equation (5a) may be approximately 2 mm. Applying a Fourier transform to equation (5a) may provide an estimate of the acoustic wave pressure distribution at the focus. (6) in and Compared with equations (4a) and (4b) f x and f yThe same. Equation (6) shows that the acoustic pressure distribution of a transducer with a circular aperture is a first-order Bessel function. In one embodiment, most of the energy is concentrated at the focal point (e.g., 15 mm from the aperture). The width of the main ultrasonic beam and the energy distribution away from the main beam can be expressed as a function of the operating frequency, as shown in Equations (4a) and (4b). In various embodiments, if the aperture is modulated (e.g., multiplied) by the correct function, two identical or nearly identical beams can be generated at the focus. In one embodiment, the cosine function can be applied to a circular aperture as follows: (7) The energy distribution or beam response at the focus of the modulated aperture in equation (7) is the convolution of the Fourier transforms of two functions of the aperture: (8) Equation (8) can be simplified to the sum of two independent functions applying the Fourier transform identity of the Dirac delta function (e.g., Identity 2 in Table 2): (9) Equation (9) shows that the two beams appearing at the focus are spatially shifted by ± , compared to the original unmodulated beams. In some embodiments, one or more other modulation functions (e.g., a sine function) may be used to achieve a desired beam response. In some embodiments, the aperture may be modulated so that more than two focal points are generated. For example, three, four, five, etc. focal points may be generated. In some embodiments, the aperture may be modulated so that the focal points are generated sequentially or approximately sequentially rather than simultaneously. In some embodiments, the treatment transducer module includes a moving mechanism configured to guide the ultrasound treatment in a linear or substantially linear sequence of individual TCPs with treatment intervals between the individual TCPs. For example, the treatment intervals may be approximately 1.1 mm, 1.5 mm, etc. In some embodiments, the transducer module may also include a moving mechanism configured to guide the ultrasound treatment in a sequence such that the TCPs are formed in a linear or substantially linear sequence separated by treatment intervals. For example, the transducer module may be configured to form TCPs along a first linear sequence and a second linear sequence separated from the first linear sequence by treatment intervals between approximately 2 mm and 3 mm. According to equation (9), if the aperture is modulated by a cosine and / or sine function of the desired spatial frequency, simultaneous or substantially simultaneous splitting of the ultrasound beam can be achieved at (or before) the focus. In one embodiment, two simultaneous or nearly simultaneous focused beams separated by a treatment interval of approximately 1.1 mm can be generated in a linear or substantially linear sequence. At an ultrasonic frequency of 7 MHz, the wavelength λ of ultrasound in water is approximately 0.220 mm. Therefore, the spatial frequency at the focus is and Expressed as: (10a) (10b) To separate the two foci by approximately 1.1 mm, the spatial frequency used to modulate the aperture is then calculated as follows. Using identities 3 and 4 from Table 2, the Fourier transform of a sine or cosine function is a Dirac delta function with parameters: (11a) In one embodiment, when the parameter is 0, equation (11a) can be solved k x : (11b) also, x o One can substitute half the separation distance (e.g., 1.1 mm): (11c) In several embodiments, a transducer having a circular aperture that transmits ultrasonic energy at various operating frequencies can be modulated by sine and / or cosine functions of the spatial frequencies listed in Table 2. The modulated aperture of the transducer can produce simultaneous or substantially simultaneous split beams with two focal points having different separation distances, as shown in Table 2. In one embodiment, the transducer can have an OD of approximately 19 mm and a focal length of approximately 15 mm. Table 2 As shown in Table 2, in several embodiments, for a given focus separation distance, the spatial frequency of the aperture modulation function increases as the ultrasonic operating frequency increases. Additionally, the spatial frequency increases as the desired focus separation distance increases. In one embodiment, higher spatial frequencies can cause amplitude transitions in the aperture to occur more quickly. Due to transducer processing limitations, rapid amplitude changes in the aperture can reduce aperture efficiency because different parts of the aperture may produce different amounts of acoustic pressure. In one embodiment, using spatial frequencies to split the beam simultaneously or nearly simultaneously can reduce the total focal gain of each beam. As shown in equation (9), the field pressure at the focus of each beam is reduced by a factor of two compared to an unmodulated beam. In one embodiment, the acoustic pressure or ultrasound intensity from the aperture can be increased to achieve similar or substantially similar intensity at the focal plane. However, in one embodiment, increasing the pressure at the aperture may not be limited by system and / or transducer processing limitations. In one embodiment, the increase in pressure at the aperture can increase the total intensity in the near field, which can increase the likelihood of overheating tissue in the treatment area located in front of the focal point. In one embodiment, the likelihood of additional heating of tissue in front of the focal point can be limited or eliminated by using lower ultrasound treatment frequencies. In one embodiment, applying the aperture modulation function as shown in equation (7) results in two simultaneous or substantially simultaneous ultrasound beams at the focal point. In various embodiments, the ultrasound beam can be split multiple times, such as three times, four times, five times, etc., so that multiple simultaneous or substantially simultaneous beams are generated. In one embodiment, four equally spaced beams along one dimension can be generated by modulating or multiplying the aperture by two independent spatial frequencies: (12a) (12b) As shown in equation (12b), an unmodulated beam at the focus can be generated at four different locations along the x-axis. In one embodiment, a constant or DC term C1 can be added to the amplitude modulation function to maintain the energy placement at the original focus position: (13a) (13b) In one embodiment, the aperture modulation of equations (12) and (13), whereby the beam can be placed at multiple locations simultaneously or nearly simultaneously, may have limited applicability due to system, material, and / or tissue limitations. In one embodiment, due to the potential for heating of tissue in the treatment region that is located in front of the focal point, the frequency of the ultrasound treatment may be adjusted (e.g., reduced) to limit and / or eliminate this potential. In one embodiment, nonlinear techniques may be applied at the focal point to limit and / or eliminate the potential for heating of tissue in front of the focal point. In one embodiment, the acoustic pressure or ultrasound intensity from the aperture may be increased to achieve a similar or substantially similar intensity at the focal plane. In various embodiments, if the amplitude and phase functions at the aperture are separable, then the sound pressure function The two-dimensional Fourier transform of U(x 1, y 1) can be expressed as x and The product of the one-dimensional Fourier transforms of the two functions of y. In various embodiments, it may be advantageous to generate multiple TCPs in a linear or substantially linear sequence, as well as to generate multiple linear sequences simultaneously or nearly simultaneously. Multibeam splitting aperture using frequency modulated electronic dithering In various embodiments, Table 2 shows the spatial frequency of the aperture used to achieve a specific distance between two simultaneous focal spots for a given operating frequency (e.g., 4 MHz, 7 MHz, 10 MHz in various embodiments). Equation (11c) shows that the separation distance between the focal spots is also a function of the operating frequency. For example, in one embodiment, the spatial frequency of the aperture (k x ) is fixed at 1.0mm -1, and allows the operating frequency to vary. Equation 11c can be rewritten to show how the focus separation distance can be modulated by the operating frequency. s = (k x z f v c ) / (πf op ) (14) where k x is the spatial frequency in mm -1 , z f is the focal depth of the aperture in mm, v c is the supersonic velocity in the propagation medium (e.g. water) in mm / μsec, and f op is the operating frequency of the aperture in MHz. In one embodiment, the following substitution is made in Equation 11c: λ = v c / f op (15) As shown in equation (14), the separation distance of the focal spots is a function of the operating frequency. In addition, the rate of change of the separation distance with respect to the operating frequency is: ds / df op =-(k x z f v c ) / (πf op 2 ) (16) Equation (16) shows that the separation distance decreases as the operating frequency increases. Table 3 (below) shows the rate of change of the separation distance as a function of operating frequency for different spatial frequencies (eg, 4 MHz, 7 MHz, 10 MHz in various embodiments). Table 3 As shown in Table 3, as the operating frequency increases, the focus becomes closer, and as the operating frequency decreases, the focus becomes farther away, without changing the phase or mechanically moving the transducer. This is a unique method of electronically moving the beam to spread the energy without relying on thermal conduction in the tissue. Benefits include a reduction or minimization of the maximum temperature and an increase in the volume of the lesion that can be thermally coagulated, without the need for additional system channels. The amount of movement from the primary operating frequency can be determined by using equation (14). In one embodiment, the primary operating frequency of the aperture is 5 MHz and the focal length is 15 mm. In some embodiments, the operating frequency is referred to as the aperture center frequency. In one embodiment, the operating frequency is 5 MHz. In one embodiment, Table 4 in FIG. 5 shows the aperture center frequency with different spatial frequencies (kx = 0.5, 1.0, 1.5, 2.0, in mm) designed for a center frequency of 5 MHz. -1 ) of the aperture. It also calculates the amount of spread of the focus from a center frequency of 5 MHz. According to one embodiment, the spacing decreases for higher frequencies relative to 5 MHz and increases for lower frequencies relative to 5 MHz. Figure 6 shows the difference in spacing of all operating frequencies of the aperture for different aperture spatial frequencies. As shown in Figure 6, the separation distance increases as the frequency decreases. In one embodiment, the separation distance is relative to a frequency of 5 MHz. In one embodiment, one way to estimate electronic jitter from frequency modulation can be determined by referencing all movements to an initial separation at 5 MHz. As shown in FIG7 , the spread of the separation distance between the foci can easily vary by more than 1 mm. In various embodiments, the range of possible operating frequencies from an aperture can be described in terms of transducer bandwidth. In one embodiment, a larger transducer bandwidth results in an aperture with a wider range of operating frequencies. The transducer bandwidth can be described as a percentage of the aperture center frequency by locating the frequency at which the transmit intensity decreases to -3dB of the peak transmit intensity. In one embodiment, the -3dB high frequency for the transmit response of the transducer aperture is designated as f -3db,H and the -3dB low frequency is designated as f -3dB, L The -3dB center frequency in [MHz] is described as: f -3dB ， center = (f -3dB ， H + f -3dB ， L ) / 2 (17) The -3dB percentage bandwidth is described as: BW -3dB = 100%* (f -3dB ， H -f -3dB ， L ) / ((f -3dB ， H +f -3dB ， L ) / 2) (18) In some embodiments, increasing the range of possible operating frequencies within an aperture can be achieved by using, but not limited to, backing layers, matching layers, multiple piezoelectric layers, electrical matching, piezoelectric composites, and / or single crystal piezoelectric ceramics. In one embodiment, as the bandwidth of the transducer increases, the range of possible separation distances increases. Table 5 (below) shows how the focal spread can change based on the percentage bandwidth if the aperture center frequency is 5 MHz. For a 0.5 mm -1 , 1.00mm -1 , 1.50mm -1 , 2.00mm -1 The spatial frequency at the aperture is 1.50mm, and the focal separation distances at 5MHz are 0.72mm, 1.43mm, 2.15mm, and 2.86mm respectively. -1and the transducer bandwidth is 60%, the separation distance between the foci varies by 1.42 mm, which is a distance greater than the lateral resolution of the beam at 5 MHz. Additional extension from the 5 MHz center frequency, in [mm] Table 5 In one embodiment, as the frequency changes, the depth of field, as well as the lateral resolution and focal gain, will also change. In one embodiment, as the frequency changes, the depth of field, lateral resolution, and focal gain will also change. Thus, in one embodiment, the intensity at the aperture can be varied based on the heating rate target. Moreover, in some embodiments, it may be advantageous to transmit multiple operating frequencies simultaneously to spread the energy immediately or nearly immediately. For example, transmit excitation of the aperture can include excitation at 4 MHz, 5 MHz, and 6 MHz, all at the same time. Multiple focal points achieved by varying the aperture spatial frequency As shown in Equation 14, the higher the aperture spatial frequency, the greater the separation distance between the foci. In one embodiment, the aperture is at a spatial frequency k x Polarization. By connecting separate electrically excited channels with the ability to modify the phase to 0 or 180 degrees, the spatial frequency can be easily doubled or reduced to zero, as shown in the embodiment of Figure 8. For example, if the phase on channels 1 to 16 is 0 degrees, the aperture spatial frequency is k x In an embodiment, when the phase on each channel varies from 0 degrees to 180 degrees such that odd channels are at 0 degrees and even channels are at 180 degrees, then the spatial frequency at the aperture is ½ k x In an embodiment, if the phase is repeated every two channels so that channels 1 and 2 are 0 degrees and channels 3 and 4 are 180 degrees, and so on, then the spatial frequency at the aperture is 0. If channel 1 is 0 degrees, channel 2 is 180 degrees, channel 3 is 180 degrees, channel 4 is 0 degrees, and so on, then the spatial frequency at the aperture is 2k x In this case, seven unique focal points can be generated. As shown in Table 4 (in Figure 5), if the aperture center frequency is 5 MHz and the aperture frequency is 0 mm -1 , 0.5mm -1 , 1.0mm -1 or 2.0mm -1If any of the phases are selected, the corresponding separation distances are 0 mm, 0.72 mm, 1.43 mm, and 2.86 mm, resulting in seven unique focal positions separated by 0.36 mm. In various embodiments, intermediate phases between 0 and 180 degrees further allow the two focal points to be tilted, so that a focal line can be generated at the focal plane. Ultimately, tilting, modulation of the focal position, and frequency modulation can heat and potentially solidify an entire line having a length of approximately 2.86 mm. In one embodiment, the polarized ceramic has a 2k x The spatial frequency of the aperture is shown in Figure 9. In this case, each electrical channel covers two polarization regions in a ceramic (e.g., piezoelectric ceramic). If channels 1 to 8 have the same electrical phase, the spatial frequency of the aperture is 2k x If the phase alternates so that odd channels have a phase of 0 degrees and even channels have a phase of 180 degrees, then the spatial frequency of the aperture is k x In one embodiment, this configuration, with only two phases possible on a channel, enables four unique focal points. In various embodiments, if additional phases are allowed, the two focal points can be tilted to many different focal positions. This configuration limits the number of electronic channels required to achieve multiple focal positions. In several embodiments, a treatment system utilizes multiple treatment channels to achieve electronic focusing and / or steering. For example, a treatment system utilizing multiple treatment channels to achieve electronic focusing and / or steering allows for faster electronic dithering to produce more thermal coagulation using the same energy as other treatment devices, or for electronic dithering to produce equivalent thermal coagulation using less energy than other treatment devices. This technology broadens the efficacy and comfort continuum provided by the device. In addition to electronic dithering, multiple treatment channels can also move the beam to different depth locations. For example, two traditional transducers, such as the DS7-4.5 (7 MHz at 4.5 mm depth) and the DS7-3.0 (7 MHz at 3.0 mm depth), can be replaced by a single device that moves between two different depths. In one embodiment, a transducer 280 (e.g., an annular array) having multiple treatment channels 281 connected to allow axial beam movement typically generates TCP 550 first at a deep depth and then moves to a shallower depth. In another embodiment, TCP 550 is generated at a shallow depth and then at a deeper depth below the skin surface. This sequentially generates TCP 550 and will result in a prolonged treatment time. For example, in one embodiment, if the time for deep TCP 550 is t deep And the time for shallow TCP 550 is t shallow , then the total treatment time for the two TCP 550 is the sum of the two treatment times, t deep Add t shallow In one embodiment, the total treatment time is reduced by forming multiple (two or more) TCPs 550 simultaneously using a signal mixing technique that uses signal apodization (masking) and phase control at each channel. In one embodiment, the total treatment time is t deep and t shallow Maximum value of: Treatment time, conventional method: t treatment = t deep + t shallow Treatment time, signal mixing: t treatment = max(t deep , t shallow ) In embodiments, an annular array design transducer 280 enables electronic shifting of the treatment beam in depth (e.g., by varying the depth of the TCP 550 below the skin surface). In one embodiment, the transducer 280 includes eight treatment channel annular transducer elements 281 with a fixed mechanical focus. FIG10 shows a top view of one embodiment of a ceramic annular array design transducer 280, with the imaging transducer 285 at the center of the bowl. In this embodiment, the treatment annular transducer 280 has eight rings labeled Tx0 through Tx7, corresponding to the elements 281. transducer In one embodiment, transducer 280 focuses spherically to one or more points. In one embodiment, transducer 280 focuses cylindrically to one or more lines. Various embodiments of transducer 280 include a flat piezoelectric device with a lens. In various embodiments, transducer 280 includes a convex side 282 and a concave side 283. In various embodiments, transducer 280 includes a convex side 282 and a concave side 283 that provide features such as variable depth, variable spacing, variable focal length positioning, and any one or more of one, two, three, four, or more simultaneous focal regions. In various embodiments, transducer 280 is electrically connected to one or more tuning circuits. The tuning circuits improve the electrical signal between the console and the transducer. In various embodiments, the one or more tuning circuits are located in the transducer housing, in the connection between the transducer and the console, and / or in the console. Figure 11 shows an embodiment of a transducer 280 comprising a single element with a convex side 282 and a concave side 283. Figure 12 shows an embodiment of a transducer 280 comprising a solid-coated convex side 282 and a striped concave side 283, wherein the strips comprise a first polarized region and a second polarized region, where the polarized regions are positive, negative, or unpolarized. Figure 12 shows an embodiment of a transducer 280 comprising a solid-coated convex side 282 and a striped concave side 283, wherein the strips comprise a first region and a second region, where the regions may or may not include a coating. In one embodiment, a single electrode is provided on the convex surface, with polarized strips on the concave surface connecting to both channels (e.g., Figure 12). The strips can be alternating to split the beam or include only one phase to simulate a conventional transducer. This allows a single transducer to emulate both DS4-4.5S and DS4-4.5 processing, thus enabling the generation of three lines with a single transducer placement. Figure 13 illustrates an embodiment of a transducer 280 comprising a striped convex side 282 and a solid-coated concave side 283, wherein the strip includes a first polarized region and a second polarized region, where the polarized regions are either positive, negative, or unpolarized. Figure 13 illustrates an embodiment of a transducer 280 comprising a striped convex side 282 and a solid-coated concave side 283, wherein the strip includes a first region and a second region, where the regions may or may not include a coating. In various embodiments, the strips are electrically connected to one or more channels. In one embodiment, odd-numbered strips are connected to the first channel, and even-numbered strips are connected to the second channel. In one embodiment, the first channel is held at 0°, while the second channel alternates between 0° and 180° (or vice versa). The focused ultrasonic energy from the first channel is maintained at a single central location, while the focused ultrasonic energy from the second (alternating) channel creates two spaced-apart focal regions. The focused ultrasonic energy from the first (constant) and second (alternating) channels together creates three simultaneous TCPs. In one embodiment, a single electrode is placed on the concave surface, with polarization strips on the convex surface connecting to both channels (e.g., Figure 13). The strips can be alternating to split the beam or include only one phase to simulate a traditional transducer. This allows a single transducer to emulate both the DS4-4.5S and DS4-4.5 processing, thus producing three lines with a single transducer placement. FIG14 illustrates an embodiment of a transducer 280 comprising a striped convex side 282 and a striped concave side 283, wherein the strip comprises a first polarized region and a second polarized region, wherein the polarized regions are positive, negative, or unpolarized, and wherein the striped regions are rotated about 90 degrees relative to one another. FIG14 illustrates an embodiment of a transducer 280 comprising a striped convex side 282 and a solid-coated concave side 283, wherein the strip comprises a first region and a second region, wherein the regions may or may not include a coating, and wherein the strips are rotated about 90 degrees relative to one another. FIG15 shows an embodiment of a transducer 280 comprising a strip-shaped convex side 282 and an annular concave side 283, wherein the strip comprises a first polarized region and a second polarized region, wherein the polarized regions are positive, negative, or unpolarized. FIG15 shows an embodiment of a transducer 280 comprising a strip-shaped convex side 282 and an annular concave side 283, wherein the strip comprises a first region and a second region, wherein the regions may or may not include a coating. FIG16 shows an embodiment of a transducer 280 comprising an annular convex side 282 and a striped concave side 283, wherein the strip comprises a first polarized region and a second polarized region, wherein the polarized regions are positive, negative, or unpolarized. FIG16 shows an embodiment of a transducer 280 comprising an annular convex side 282 and a striped concave side 283, wherein the strip comprises a first region and a second region, wherein the regions may or may not comprise a coating. In some embodiments, the system includes various features that exist as a single feature (as opposed to a plurality of features). For example, in one embodiment, the system comprises, consists essentially of, or includes a single ultrasonic transducer element adapted to provide two simultaneous treatment zones via dithering. In alternative embodiments, multiple features or components are provided. Simultaneous treatment at multiple depths In various embodiments, the treatment system is configured to produce multiple microcoagulation zones in tissue separated by equal distances along a line of mechanical motion. In various embodiments, the treatment system provides different modules, cartridges, or different transducers (e.g., DS4-4.5, DS7-4.5, DS7-3.0, DS10-1.5, DS7-3.0N, DS10-1.5N or OT4-4.5, OT7-4.5, OT7-3.0, OT10-1.5, where the first digit represents the treatment frequency and the second digit represents the depth of treatment delivery. The 'N' for the last two transducers indicates that the device is a narrow transducer, which is used in hard-to-reach areas, such as around the nose and mouth. The first four transducers can deliver treatment along a 25 mm line, while the narrow transducer provides a maximum line length of 14 mm). In various embodiments, a transducer with a ring electrode and a poled ceramic can implement frequency dithering in the lateral dimension, electronic dithering in the depth dimension, and electronic focusing in the depth dimension, as well as a single transducer capable of emulating the DS10-1.5 (10 MHz at 1.5 mm depth), DS7-3.0 (7 MHz at 3.0 mm depth), DS7-4.5 (7 MHz at 4.5 mm depth), and DS4-4.5 (4 MHz at 4.5 mm depth) in a single transducer. In one embodiment, optional tuning electronics can be used in combination with the composite ceramic to enable the transducer with a ring electrode and poled ceramic to implement frequency dithering in the lateral dimension, electronic dithering in the depth dimension, and electronic focusing in the depth dimension. In various embodiments, one, two, three, or more optional tuning circuits help stabilize the signal between the console and the transducer and can be present in the transducer housing, between the transducer and the console, or in the console itself. In one embodiment, a full-face treatment uses a transducer to deliver 800 treatment lines, which involves the operator moving the handset along the patient's skin over approximately 70 to 90 minutes. In one embodiment, a single treatment bowl is configured to deliver two treatment lines simultaneously (e.g., DS4-4.5S, DS4-3.0S, OT4-4.5S, or OT4-3.0S), which, based on recent clinical studies, can reduce treatment delivery time by approximately 40%. In various embodiments, when operated at the correct energy levels, the treatment device provides comparable levels of efficacy. In various embodiments, simultaneous treatment reduces the overall pain of the treatment. In one embodiment, simultaneous treatment time is significantly shortened, assuming less overall pain during treatment. In various embodiments, simultaneous treatment increases treatment speed by 10%, 20%, 25%, 30%, 40%, 50%, 60% or more. In various embodiments, simultaneous treatment reduces treatment time by 10%, 20%, 25%, 30%, 40%, 50%, 60% or more. In various embodiments, the system is configured to complete treatment time in 60, 50, 40, 30, 20, or 10 minutes or less. In one embodiment, a simultaneous treatment system generates two lines simultaneously, with the ability to shift the microcoagulation depth at the thermal coagulation zone 550. In one embodiment, the bandwidth of the treatment transducer is increased, making it possible to have a device that behaves like two, three, four, five, or six fixed depth devices. In one embodiment, an 8-channel treatment device is used. FIG17 shows an embodiment of a transducer 280 comprising an annular convex side 282 and a strip-shaped concave side 283, wherein the strip comprises a first polarized region and a second polarized region, wherein the polarized regions are positive, negative, or unpolarized. FIG17 shows an embodiment of a transducer 280 comprising an annular convex side 282 and a strip-shaped concave side 283, wherein the strip comprises a first region and a second region, wherein the regions may or may not include a coating. In one embodiment, an annular array coupled with simultaneous transducers enables the transduction of the transducer at different depths 279 below the skin surface (e.g., D 1. D 2. D 3. ... D N ) produces two focused ultrasound treatment lines simultaneously. In one embodiment, the strips on the concave side 283 are alternately polarized (e.g., at 0 degrees and 180 degrees, etc.). In various embodiments, the depth 279 is 1.5 mm, 3.0 mm, 4.0 mm, 4.5 mm, or 7 mm. In one embodiment, D 1 = 1.5 mm, D 2 = 3.0 mm and D = 4.5 mm. In various embodiments, depth 279 is 0.5 mm, 1.0 mm, 1.5 mm, 2 mm, 3 mm, 4 mm, 4.5 mm, 6 mm, 7 mm, less than 3 mm, between 0.5 mm and 5 mm, between 1.5 mm and 4.5 mm, greater than 4.5 mm, greater than 6 mm, 7 mm, and any point within the ranges of 0.1 mm-3 mm, 0.1 mm-4.5 mm, 0.1 mm-25 mm, 0.1 mm-100 mm, and any depth therein (e.g., 6 mm, 7 mm, 10 mm, 13 mm, 15 mm, 17 mm). In embodiments, simultaneous treatment at multiple depths produces multiple thermally coagulated regions 550 at different depths 279. FIG17 illustrates an embodiment of simultaneously treating both sides of a bowl. On one side of the treatment bowl are strips for performing alternating polarization. In one embodiment, the strips are on the concave side 283. In another embodiment, the strips are on the convex side 282. In one embodiment, after polarization is complete, the electrodes are stripped and a complete electrode is placed on the entire side. In one embodiment, a cold silver electrode can also be used to connect the strips. In one embodiment, opposite sides of the treatment bowl include concentric rings that may or may not have equal areas. When the correct phase is applied to the treatment bowl, the annular array enables beam movement in depth. In one embodiment, transducer 280, comprising an annular convex side 282 and a strip-shaped concave side 283, is configured to generate multi-depth thermal coagulation zones 550 at various depths 279, as shown in FIG18 (projected in xyz space), FIG19 (xz plane), and FIG20 (yz plane). FIG18 shows a three-dimensional sketch of the microcoagulation points. In one embodiment, two, three, four, or more points can be generated simultaneously. In one embodiment, two points are generated simultaneously. In one embodiment, it is contemplated that a deeper microcoagulation point (e.g., 4.5 mm) is generated first before moving to the next depth (e.g., 3.0 mm) and then ultimately to the shallowest depth (e.g., 1.5 mm). In one embodiment, the motion mechanism moves from left to right and vice versa. In one embodiment, the temperature of the skin can be limited by forming a microcoagulation point at the deepest depth (e.g., 4.5 mm) when moving from left to right, then placing the next depth (e.g., 3.0 mm) when moving from right to left, and then completing the treatment with the microcoagulation point at the shallowest depth (e.g., 1.5 mm) when moving from left to right again. Figure 19 shows a projection of the treatment along the direction (x-axis) and depth (z-axis) of the mechanical movement. Figure 20 shows a projection of the treatment along the direction (y-axis) and depth (z-axis) of the beam splitting. Figures 21-23 illustrate an embodiment of a simultaneous multi-depth treatment device configured to produce TCP at depths of 1.5 mm, 3.0 mm, and 4.5 mm, with intermediate layers offset between deep and shallow depths. In one embodiment, a transducer 280, comprising an annular convex side 282 and a strip-shaped concave side 283, is configured to produce multiple deep thermal coagulation zones 550 at various depths 279, as shown in Figures 21 (projected in xyz space), 22 (xz plane), and 23 (yz plane). In one embodiment, the length of the TCP may limit the ability to stack TCP treatments at multiple depths directly on top of each other. In one embodiment, a motion mechanism offsets TCP treatments at different depths. Figure 21 shows a three-dimensional view of an offset multi-depth transducer. A similar delivery process described for Figures 18-20a can be applied to the embodiments of Figures 21-23, where microcoagulation points can be delivered while moving from left to right or right to left to minimize any potential damage to the epidermis, dermis, or other tissue layers. Figure 22 shows a projection of the delivery along the mechanical motion (x-axis) and depth (z-axis). This clearly shows the displacement of the middle layer of the TCP from the deep and shallow treatments. Figure 23 shows a projection of the delivery along the direction of beam splitting (y-axis) and depth (z-axis). Figures 24-26 illustrate an embodiment of a simultaneous multi-depth treatment device configured to produce TCPs at depths of 1.5 mm, 3.0 mm, and 4.5 mm, with the intermediate layer offset from the shallow depth at varying pitches. In one embodiment, a motion mechanism can be used to match the separation distance between TCPs in a single-line treatment. Figures 24-26 show a three-dimensional sketch of a simultaneous multi-depth treatment. In this embodiment, the 4.5 mm depth treatment is delivered at one pitch (1.5 mm apart), while the 3.0 mm and 1.5 mm depth treatments are delivered at another pitch (e.g., 1.1 mm apart). Although the 1.5 mm and 3.0 mm depth treatments are at the same pitch (e.g., 1.1 mm), the motion mechanism allows for an offset to prevent stacking of microcoagulation points. Figure 25 shows a projection of the delivery along the mechanical motion (x-axis) and depth (z-axis). This clearly shows that the intermediate layer of the TCP is offset from the shallow treatment, even though the pitch is the same. Similarly, the deepest treatment is at a slightly larger pitch than the other two depths. Figure 26 shows projections of delivery along the direction (y-axis) and depth (z-axis) of beam splitting. In various embodiments, a transducer 280 comprising an annular convex side 282 and a strip-shaped concave side 283 (e.g., as shown in FIG. 16 and / or FIG. 17 ) produces the treatment patterns shown in the embodiments of FIG. 25 , 26 , and / or 29 . In embodiments, when viewed in projection in xyz space, the transducer 280 having an annular convex side 282 and a strip-shaped concave side 283 produces an intensity peak near the center of the focal region (e.g., in FIG. 18 and 19 ), where each ring within the annular convex side 282 is controlled with an amplitude (A) and phase (θ). In this case, the polarization of the strips creates simultaneous focal spots at a single depth. To create simultaneous focal spots at each depth, as shown in FIG. 18 and 19 , different phases (θ) and different amplitudes (A) are applied to each ring to create simultaneous focal spots at different depths. The different phases enable the two focal spots to be moved to different focal depths, while the different amplitudes allow the focal spot intensities to vary, thereby altering the heating rate in the tissue. The amount of separation between two foci at the same depth along the Y axis is determined by the frequency, focal depth, and spatial frequency of the strip (see Equation 14, where s is solved). The transducer can be moved manually or mechanically to precisely space simultaneous foci along the X axis. In one embodiment, the middle ring has an amplitude A 1, greater than the magnitude A The next outer ring of 2, A 2 is greater than A 3, ... until the outermost ring amplitude A n , producing a wider intensity range and capable of shaping into two simultaneous foci. This amplitude control allows for variations in the beam width at both foci as well as the intensity, which influences the heating rate. In various embodiments, a continuous wave function can be used to generate simultaneous focused regions at different depths below the skin surface that combines the excitation function of the focused solution with another solution. In one embodiment, the first depth (d 1) in the focal area (f 1) with a different first depth (d 1) The second depth (d The second focal area (f 2) Generated simultaneously. Different depths (d 1 and d The two focal points at 2) can be generated simultaneously via a linear system that combines excitation with a single ultrasonic transducer element. The following table shows the two sets of amplitudes and phases required for each focal region and depth. Since the two excitations occur at the same frequency, the two excitations on each ring can be combined into one amplitude and one phase. Assume that the excitation on ring 1 for focus #1 is written as: 1 ， 1(t) = A 1 ， 1sin(ωt + θ 1 ， 1) Assume that the excitation on ring 1 at focus #2 is written as: 1 ， 2(t) = A 1 ， 2sin(ωt + θ 1 ， 2) where ω is 2πf, where f is frequency and t is time. In order to produce two focal spots at two different depths simultaneously, the two excitations of the first ring must be combined: X 1(t) = x 1 ， 1(t) + x 1 ， 2(t) = A 1 ， 1sin(ωt + θ 1 ， 1) + A 1 ， 2sin(ωt + θ 1 ， 2) However, even if this is the necessary excitation on loop 1, it is unclear what the actual amplitude and phase required on the loop to properly excite f 1 and f 2. To determine the new magnitude of the combined effect (Λ 1) and the new phase (Ω 1), applying the following trigonometric identities: Λ 1= sqrt([A 1 ， 1cos(θ 1 ， 1) + A 1 ， 2cos(θ 1 ， 2)] 2 + [A 1 ， 1sin(θ 1 ， 1) + A 1 ， 2sin(θ 1 ， 2)] 2 ) Ω 1 = tan -1 [(A 1 ， 1sin(θ 1 ， 1) + A 1 ， 2sin(θ 1 ， 2)) / (A 1 ， 1cos(θ 1 ， 1) + A 1 ， 2cos(θ 1 ， 2))] The new excitation on ring 1 is: X 1(t) = Λ 1sin(ωt + Ω 1) The same process can be applied to other rings to obtain array solutions to simultaneously produce f 1 and f 2. Similarly, if it is desired to deliver three or more foci simultaneously, the process can be repeated using the above identities until only one excitation and one phase are calculated for each ring. For example, assuming the goal is to generate three foci simultaneously, an initial new amplitude and phase for each ring are calculated based on the amplitude and phase required for Focus 1 and Focus 2. Next, these new amplitudes and phases are combined with the ring excitation required for Focus 3. Although simultaneous foci can be generated using this method, the necessary amplitude may be limited by piezoelectric material saturation and the ability of the tissue to absorb the increased intensity in surrounding tissue when generating multiple foci. These physical limitations must be compared with the temporal advantages of generating foci simultaneously. Figures 27-29 illustrate an embodiment of a simultaneous multi-depth treatment device configured to generate TCPs at depths of 1.5 mm, 3.0 mm, and 4.5 mm, with intermediate layers offset from shallow depths and frequency used to create different separation distances at each depth. In Figures 24-26, a motion mechanism is used to shift the intermediate depths of the TCPs from the deepest and shallowest depths. In various embodiments, the amount of separation between the simultaneously generated TCPs depends on the treatment frequency. In one embodiment, the device is capable of delivering treatment at multiple frequencies (e.g., using a broadband treatment transducer), and the distance between the TCPs can be modulated using frequency. As discussed with respect to Figure 18, the spacing of the strips is determined at the time of manufacture because it is generated by ceramic polarization. Lower frequencies and deeper depths produce wider separation between the simultaneously generated TCPs (in the yz plane). Figure 4a shows a three-dimensional matrix of TCPs with these varying degrees of separation. As the frequency increases and the treatment depth decreases at shallower depths, the distance between the simultaneously generated TCPs decreases. Figure 28 shows projections of the delivery along the mechanical motion (x-axis) and depth (z-axis). This clearly shows the shift in the middle layer of TCPs from shallow and deep treatments, even though the pitch is the same. Figure 29 shows a projection of the delivery along the direction (y-axis) and depth (z-axis) of the beam split. The projection shows that the spacing between TCPs becomes larger as the treatment depth increases, which is mainly due to the depth and frequency changes in the treatment. In one embodiment, as shown in Figure 29, different spacings can be generated by changing the frequency and focal depth. For example, Equation 14 is: s = (2 k x z f λ) / (2π) where s is the separation between two simultaneous focal spots at the same depth. This equation shows that the focal separation is a function of focal depth (zf) and frequency (since λ is the speed of sound divided by frequency). This assumes the same frequency and spatial frequency across the strip. The table summarizes the separation for different focal spots separated by 1.5 mm. However, if the frequency is varied so that higher frequencies are used for the shallowest focus, a wider range of separation distances can be achieved: In various embodiments, different w (e.g., w1, w2) can be used to vary the distance or spacing. In various embodiments, a continuous wave function can be used to generate simultaneous focal regions at different depths below the skin surface, combining frequency with Fourier transforms. In one embodiment, the first depth (d 1) focal area (f 1) with a different first depth (d 1) The second depth (d 2) at the second focal area (f 2) Generated simultaneously. Different depths (d 1 and d 2) The two focal points at can be generated simultaneously via a linear system, which combines the excitation of a single ultrasonic transducer element. f 1_____ f 2_____ A 1 ， 1 / θ 1 ， 1A 1 ， 2 / θ 1 ， 2A 2 ， 1 / θ 2 ， 1A 2 ， 2 / θ 2 ， 2A 3 ， 1 / θ 3 ， 1A 3 ， 2 / θ 3 ， 2A 4 ， 1 / θ 4 ， 1A 4 ， 2 / θ 4 ， 2 of which X 1 = excitation (A, θ) = A 1,1 sin (w 1t-θ 1,1 ) A 1,2 sin (w 2t-θ 1,2 ) to produce two simultaneous focal points at different distances. In various embodiments, when a sufficient DC bias is applied to the material, the electrostrictor exhibits piezoelectric behavior. In one embodiment, the strength of the piezoelectric behavior is proportional to the acoustic sensitivity. In one embodiment, the electrostrictive material is used with the treatment bowl during the manufacturing process. In one embodiment, patterning and electrode attachment are performed during manufacturing, but polarization of the electrostrictor is completed during treatment delivery. For example, in one embodiment, the transmit aperture can be a square wave, as shown in FIG37, or masked by modifying the high voltage value. FIG30 illustrates an embodiment of a simultaneous multi-depth treatment device configured to generate TCP at depths of 1.5 mm, 3.0 mm, and 4.5 mm, wherein an annular array is coupled to an electrostrictor capable of simultaneously generating multiple pairs at different depths. In one embodiment, the electrostrictor modulates spatial frequency (such as shown in one embodiment in FIG37) to generate a treatment line (such as shown in one embodiment in FIG34). In one embodiment, the electrostrictor generates the treatment line without a mechanical motion mechanism. In one embodiment, the electrostrictor generates the line perpendicular to the motion of the mechanical motion mechanism. Thus, in various embodiments, multidimensional therapy can produce one, two, or more therapeutic focal zones at various intervals, along lines, planes, or in three-dimensional space. In some embodiments, an electrostrictor causes ions in the piezoelectric transducer's lattice to displace when exposed to an external electric field. In various embodiments, Figures 17-29 depict a fixed polarization pattern to produce a separation distance between two simultaneously generated TCPs. This is because the polarization pattern is generated within the piezoelectric ceramic during the manufacturing process. The spacing between the strips determines the spacing between the TCPs. The greater the distance between the strips, the closer the TCPs are. In some embodiments, the distance between the strips cannot be changed after polarization is complete. In one embodiment, as shown in Figures 30-33, the electrically insulating material is not polarized. Instead, an electrostrictor is used to apply a direct current (DC) voltage during device operation to exhibit piezoelectric behavior that can be used to improve device performance. Figure 5a shows the front and back sides (e.g., concave and convex sides) of a ceramic bowl, similar to the embodiment shown in Figure 17. In one embodiment, the annular pattern is on the back side (e.g., convex side) of the transducer. Compared to the embodiment in Figure 17 , the front side (patient side, e.g., concave side) is slightly different; for example, the strips appear to be produced with a finer pitch. Secondly, the ceramic is not poled. Instead, the connections from each individual strip are connected to an independent set of electronics, which applies a voltage to the strip to produce the appropriate pattern that creates the separation distance between TCPs. In one embodiment, the voltage varies at a high spatial frequency, resulting in a greater separation distance between TCPs. The electronics allow this pattern to be varied, allowing the distance between TCPs to also vary. The result is a collection of simultaneous TCPs that can be generated through this amplitude modulation. It is not necessary to apply a negative or positive voltage to each strip.In some embodiments, shorting the strips to ground can prevent or reduce acoustic excitation. Figure 31 illustrates an example of the type of TCP distribution that can be generated in three dimensions. In one embodiment, five TCPs are generated at each depth using three different DC amplitude modulation patterns on the strips. Again, the sequence can vary within depth 279 or at each depth, depending on the motion mechanism's movement from left to right or right to left, the modulation pattern, and the focusing of the ring. The sequence used is based on the safe tolerance of the epidermis and dermis, as well as any other tissue layers, and the goal of delivering the TCPs as quickly as possible. Figure 32 shows a projection of delivery along the mechanical motion (x-axis) and depth (z-axis). Figure 33 shows a projection of delivery along the direction of beam splitting (y-axis) and depth (z-axis). The projection shows the five TCPs generated in that plane. Two pairs of TCPs are generated simultaneously, with one pair generated at a time, similar to conventional transducers. In various embodiments, the techniques discussed for the embodiments of Figures 21-29 are applicable to electrostrictor designs. Figures 34-36 illustrate an embodiment of a simultaneous multi-depth treatment device configured to generate TCP at depths of 1.5 mm, 3.0 mm, and 4.5 mm, wherein an annular array coupled to a simultaneous treatment transducer enables the simultaneous generation of two lines at different depths. In one embodiment, an advantage of using an electrostrictor with sufficient strips is the ability to generate thermal treatment lines if the pattern changes rapidly. Figure 34 illustrates an embodiment showing three-dimensional TCP lines generated using multiple spatial frequencies of the electrostrictor pattern at only one depth. Depending on the rate of pattern change across the strips, the heating can be varied to produce microcoagulation lines or hyperthermia lines, which are tissues used for apoptosis. Figure 35 illustrates a projection onto the xz plane, which considers five lines. Figure 36 illustrates a projection onto the yz plane, which shows the heated lines along the y-axis at a specific depth. In one embodiment, Figure 37 illustrates different patterns that can be generated when the strips have a fine pitch. In Figure 37, the x-axis represents the distance across the transducer. The y-axis represents the DC amplitude at a location across the transducer. In various embodiments, various DC signals applied across the transducer can result in different spacings between focal spots. In one embodiment, the fine pitch is related to the desired splitting distance, operating frequency, and depth of focus. In various embodiments, the fine pitch is between 0.1 mm and 0.05 mm (e.g., 100 microns to 50 microns, including 90, 80, 70, 60 microns, and any values ​​therebetween). The figure illustrates amplitude modulation along the y-axis for different spacings of micro-coagulation points. While the figure covers factors of 2, other modulation patterns between the multiples shown are possible. Modulation patterns do not have to be integers of the 1x pattern. In various embodiments, even, odd, and zero patterns are possible. Finally, the electrostrictor approach also offers the possibility of modulating amplitude patterns because polarization is a strong function of the DC bias voltage. Various advantages of embodiments of a simultaneous multi-depth treatment device configured to generate multiple TCPs at different depths include generating simultaneous TCPs at multiple depths. In one embodiment, an advantage is eliminating multiple transducers, thereby reducing transducer swapping by the operator. In one embodiment, an advantage is faster treatment time. In one embodiment, an advantage is delivering the same number of lines with fewer button presses. In one embodiment, an advantage is modulating the distance between simultaneously delivered TCPs. In one embodiment, an advantage is maintaining the pitch separation of TCPs at each depth along the mechanical motion line. In one embodiment, an advantage is avoiding pulse stacking at multiple depths. In one embodiment, an advantage is the ability to generate larger coagulation and apoptosis zones. In one embodiment, an advantage is the ability to deliver microcoagulation lines in three dimensions. In one embodiment, an advantage of using an electrostrictor includes generating more than two lines with a single transducer placed on the patient's body. In one embodiment, an advantage of using an electrostrictor is modulating the distance between simultaneously delivered TCPs. In one embodiment, an advantage is the ability to modulate the attenuation of spatial high-frequency harmonics from the simultaneous treatment modulation pattern. In one embodiment, an advantage of using an electrostrictor provides the possibility of adding zeros to the modulation pattern. Some embodiments and examples described herein are examples and are not intended to limit the full scope of the compositions and methods described herein. Some embodiments, equivalent changes, modifications and variations of materials, compositions and methods can be made within the scope of the present invention with substantially similar results. While the present invention is susceptible to various modifications and alternative forms, specific examples thereof are shown in the drawings and described in detail herein. However, it should be understood that the invention is not limited to the specific forms or methods disclosed, but rather, the invention is intended to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the various embodiments described and the appended claims. Any method disclosed herein need not be performed in the order described. The methods disclosed herein include certain actions taken by the practitioner; however, they may also, explicitly or implicitly, include any third-party instructions for these actions. For example, an action such as "coupling the transducer module to the ultrasound probe" includes "instructing the transducer module to couple to the ultrasound probe." The ranges disclosed herein also encompass any and all overlapping, sub-ranges, and combinations thereof. Phrases such as "at most," "at least," "greater than," "less than," and "between" include the stated number. A number following a term such as "about" or "approximately" includes the stated number. For example, "about 25 mm" includes "25 mm." 10: Region of Interest 20: Ultrasonic System / System 50: Ultrasonic Energy 100: Handheld Wand 100': Handheld Wand 100'': Handheld Wand 130: Interface 140: Controller or Switch 145: Connector 150: Imaging Controller / Controller or Switch 160: Thermal Treatment Controller / Controller or Switch 200: Module 200': Module 200'': Module 230: Acoustically Transparent Component 235: Interface Guide 254: Treatment Area 270: Offset Distance 278: Depth of Focus 279: Tissue Depth / Depth 280: Ultrasonic Transducer / Transducer 281: Treatment Channel / Treatment Channel Annular Transducer Element / Element 282: Convex Side 283: Concave Side 285 : Imaging transducer 290 : Direction / First Direction / Arrow 291 : Arrow 295 : Compartment 300 : Controller / Console 300 ': Controller 300'': Controller 301 : Cart 302 : Compartment 310 : Graphic Display / Display / Graphical User Interface / Graphical Interface 320 : Access Key 400 : Motion Mechanism 401 : Lead Screw 402 : Encoder 403 : Motor 500 : Subject 501 : Skin Surface / Surface / Skin 502 : Epidermis 503 : Dermis 504 : Hypodermis 505 : Fat Layer 507 : Superficial Musculoaponeurotic System / SMAS / SMAS Layer 509 : Muscle Layer 525 : Treatment Area 550 : Thermal Coagulation Point or Zone (TCP) D1 : Depth D2 : Depth D3 : Depth Tx0 : Ring Tx1 : Ring Tx2 : Ring Tx3 : Ring Tx4 : Ring Tx5 : Ring Tx6 : Ring Tx7 : Ring The drawings described herein are for illustration purposes only and are not intended to limit the scope of the present disclosure in any way. Embodiments of the present invention will be more fully understood from the detailed description and accompanying drawings, in which: [FIG. 1A] is a schematic diagram of an ultrasonic system according to various embodiments of the present invention. [FIG. 1B] is a schematic diagram of an ultrasonic system according to various embodiments of the present invention. [FIG. 1C] is a schematic diagram of an ultrasonic system according to various embodiments of the present invention. [ FIG. 2 ] is a schematic diagram of an ultrasound system coupled to a region of interest according to various embodiments of the present invention. [Fig. 3] is a schematic diagram of a portion of a transducer according to various embodiments of the present invention. [ Fig. 4 ] is a partially cutaway side view of a supersonic system according to various embodiments of the present invention. [ FIG. 5 ] is a table showing focus separations of apertures having different spatial frequencies according to various embodiments of the present invention. [ FIG. [ FIG. 6 ] is a graph showing focus separation of apertures having different aperture spatial frequencies according to various embodiments of the present invention. [ FIG. [ FIG. 7 ] is a graph showing focus separation of apertures having different aperture spatial frequencies according to various embodiments of the present invention. [ FIG. [FIG. 8] is a schematic diagram of aperture polarization with spatial frequency that can be modified by an excitation channel according to various embodiments of the present invention. [ FIG. 9 ] is a schematic diagram of a polarized ceramic having a spatial frequency that can be modified by exciting a channel covering two polarized regions of the ceramic according to various embodiments of the present invention. [ FIG. 9 ] FIG. [Fig. 10] is a schematic diagram of an embodiment of an array transducer having an imaging transducer. [ Fig. 11 ] is a schematic diagram of a transducer viewed from a convex side, a side cross section, and a concave side according to various embodiments of the present invention. [ Fig. 12 ] is a schematic diagram of a transducer viewed from a convex side, a side cross section, and a concave side according to various embodiments of the present invention. [ Fig. 12 ] [ Fig. 13 ] is a schematic diagram of a transducer viewed from a convex side, a side cross section, and a concave side according to various embodiments of the present invention. [ Fig. 14 ] is a schematic diagram of a transducer viewed from a convex side, a side cross section, and a concave side according to various embodiments of the present invention. [ Fig. 14 ] [ Fig. 15 ] is a schematic diagram of a transducer viewed from a convex side, a side cross section, and a concave side according to various embodiments of the present invention. [ Fig. 15 ] [ Fig. 16 ] is a schematic diagram of a transducer viewed from the convex side, side cross-section, and concave side according to various embodiments of the present invention. [ Fig. 16 ] [ Fig. 17 ] is a schematic diagram of a transducer viewed from the convex side and the concave side according to various embodiments of the present invention. [FIG. 18] is a schematic diagram of multiple thermal coagulation zones at various depths produced by a transducer according to various embodiments of the present invention. [FIG. 18] FIG. 19 is a schematic diagram of the xz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG. 18 . FIG. 20 is a schematic diagram of the yz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG. 18 . [FIG. 21] is a schematic diagram of multiple thermal coagulation zones at various depths produced by a transducer according to various embodiments of the present invention. FIG. 22 is a schematic diagram of the xz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG. 21 . FIG. 23 is a schematic diagram of the yz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG. 21 . [FIG. 24] is a schematic diagram of multiple thermal coagulation zones at various depths produced by a transducer according to various embodiments of the present invention. FIG. 25 is a schematic diagram of the xz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG. 24 . FIG. 26 is a schematic diagram of the yz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG. 24 . [Figure 27] is a schematic diagram of multiple thermal coagulation zones at various depths produced by a transducer according to various embodiments of the present invention. FIG28 is a schematic diagram of the xz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG27 . FIG. 29 is a schematic diagram of the yz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG. 27 . [Fig. 30] Fig. 30 is a schematic diagram of a transducer viewed from the convex side and the concave side according to various embodiments of the present invention. [Figure 31] is a schematic diagram of multiple thermal coagulation zones at various depths produced by a transducer according to various embodiments of the present invention. FIG32 is a schematic diagram of the xz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG31 . FIG33 is a schematic diagram of the yz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG31 . [Figure 34] is a schematic diagram of multiple thermal coagulation zones at various depths produced by a transducer according to various embodiments of the present invention. FIG35 is a schematic diagram of the xz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG34 . FIG36 is a schematic diagram of the yz plane of multiple thermal coagulation zones at various depths generated by the transducer according to FIG34 . [Figure 37] is a graph showing amplitude and DC corresponding to focal plane focus produced by a transducer according to various embodiments of the present invention. 20:Supersonic system / system 100:Handheld stick 300: Controller / Console 301: Cart 310: Graphics Display / Display / Graphical User Interface / Graphical Interface

Claims

1. An ultrasonic system for transmitting ultrasound at multiple locations, comprising: Module, It includes an ultrasound transducer and an access key connected to the module, the access key being configured to transmit data from a remote provider to the ultrasound system to control the functionality of the module, wherein the ultrasound transducer is adapted to apply ultrasound treatment at a plurality of spaced-apart locations, wherein the plurality of spaced-apart locations are positioned in a linear sequence and separated by intervals that jitter via frequency oscillation, and wherein, in the presence of connectivity, the access key provides system security, region-specific access to treatment guidelines, software upgrades, support for log transmission, credit transfer, and data storage.

2. The ultrasound system according to claim 1, wherein, The module includes a wireless connection to the Internet via one or more of the following: Wi-Fi, cellular modem, and Bluetooth.

3. The ultrasound system according to claim 1, wherein, The ultrasonic transducer is adapted to apply the ultrasonic treatment to tissue at one or more focal depths at the plurality of spaced locations.

4. The ultrasound system according to claim 1, wherein, The ultrasonic transducer is polarized using at least a first polarization configuration and a second polarization configuration.

5. The ultrasound system according to claim 1, further comprising a control module for controlling the ultrasound transducer, wherein the control module modifies the position between the positions of the plurality of intervals by jittering the first and second focusing regions, wherein the jittering includes an interval distribution mechanically and / or electronically dispersed between the first and second focusing regions.

6. The ultrasound system according to claim 5, wherein, The first set of positions among multiple intervals is located within a first cosmetic treatment area, and the second set of positions among multiple intervals is located within a second cosmetic treatment area, wherein the first cosmetic treatment area is different from the second cosmetic treatment area.

7. The ultrasound system according to claim 1, wherein, The ultrasonic transducer includes a piezoelectric material, and multiple portions of the ultrasonic transducer are adapted to generate multiple corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer.

8. The ultrasound system according to claim 1, wherein, The ultrasonic transducer is adapted to apply the ultrasonic therapy using amplitude modulation, wherein multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity amplitudes, wherein a first amplitude is different from a second amplitude.

9. The ultrasound system according to claim 1, wherein, The ultrasonic transducer is adapted to apply the ultrasonic therapy via a phase shift, wherein multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity phases, wherein a first phase is different from a second phase.

10. An ultrasound therapy system for delivering ultrasound at multiple locations, comprising: An ultrasound transducer adapted to apply ultrasound therapy to tissue at one or more depths of focus at multiple intervals, wherein the ultrasound transducer is polarized using at least a first polarization configuration and a second polarization configuration; a control module for controlling the ultrasound transducer; and an access key configured to transmit data from a remote provider to the ultrasound therapy system to control the functions of the ultrasound therapy system via the control module, wherein, in the presence of connectivity, the access key provides system security, region-specific access to treatment guidelines, software upgrades, support for log transmission, credit transfer, and data storage, wherein the control module modifies the position between the multiple intervals by jittering a first and a second focusing region, wherein the jittering includes mechanically and / or electronically dispersing the interval distribution of the positions of the first and second focusing regions, and wherein the interval distribution is separated by intervals jittered via frequency oscillation.

11. The ultrasound therapy system according to claim 10, wherein, The first set of positions among multiple intervals is located within a first cosmetic treatment area, and the second set of positions among multiple intervals is located within a second cosmetic treatment area, wherein the first cosmetic treatment area is different from the second cosmetic treatment area.

12. The ultrasound therapy system according to claim 10, wherein, The ultrasonic transducer includes a piezoelectric material, and multiple portions of the ultrasonic transducer are adapted to generate multiple corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer.

13. The ultrasound therapy system according to claim 12, wherein, The plurality of corresponding piezoelectric material changes include at least one of piezoelectric material expansion and piezoelectric material contraction.

14. The ultrasound therapy system according to claim 10, wherein, The ultrasonic transducer is adapted to apply the ultrasonic therapy using amplitude modulation, wherein multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity amplitudes, wherein a first amplitude is different from a second amplitude.

15. The ultrasound therapy system according to claim 13, wherein, At least a portion of the ultrasonic transducer is adapted to emit the ultrasonic therapy at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the piezoelectric material varies over time.

16. The ultrasound therapy system according to claim 10, wherein, The ultrasonic transducer is adapted to apply the ultrasonic therapy via a phase shift, wherein multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity phases, wherein a first phase is different from a second phase.

17. The ultrasound therapy system according to claim 10, wherein, The ultrasonic transducer is further adapted to: apply the ultrasonic therapy using amplitude modulation, whereby multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity amplitudes, wherein a first amplitude is different from a second amplitude; and apply the ultrasonic therapy, whereby multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity phases, wherein a first phase is different from a second phase.

18. The ultrasound therapy system according to claim 10, wherein, The ultrasound treatment is at least one of the following: face lifting, eyebrow lifting, chin lifting, eye treatment, wrinkle reduction, shoulder improvement, buttock lifting, scar reduction, burn treatment, skin tightening, vascular reduction, sweat gland treatment, sunspot removal, fat treatment, abdominal laxity treatment, and cellulite treatment.

19. The ultrasound therapy system according to claim 10, wherein, The ultrasound transducer includes a moving mechanism adapted to guide the ultrasound treatment in at least one pair of simultaneous sequences within a separate thermo-cosmetic treatment area.

20. The ultrasound therapy system according to claim 10, wherein, The ultrasound transducer is configured for ultrasound imaging and ultrasound therapy.

21. The ultrasound therapy system according to claim 10, wherein, The ultrasound transducer includes a transducer module adapted to apply the ultrasound therapy.

22. A method for transmitting ultrasound, the method comprising: An ultrasound probe comprising a control module and an access key for an ultrasound therapy system are provided. The access key is configured to transmit data from a remote provider to the ultrasound therapy system to control the functions of the ultrasound therapy system via the control module. During connectivity, the access key provides system security, region-specific access to treatment guidelines, software upgrades, support for log transmission, credit transfer, and data storage. The ultrasound probe is adapted to apply ultrasound therapy to tissue at one or more focal depths at multiple intervals. The control module is configured to modify a first focal region among the one or more focal regions by dithering through a modulation frequency to change the size or position of the first focal region in the tissue. The dithering includes mechanically and / or electronically dispersing the interval distribution of the positions of the one or more focal regions by changing the frequency, and the one or more focal regions are separated by intervals dithered via frequency oscillation.

23. The method according to claim 22, wherein, The second focusing region in one or more focusing regions is emitted from a single transducer element.

24. The method according to claim 22, further comprising imaging the first focused region with an ultrasonic imaging element.

25. The method according to request item 22, wherein, The frequency modulation is in the range of 1% to 50%.

26. The method according to claim 22, wherein, The method is designed to work non-invasively to treat the tissue.

27. The method according to any one of claims 22 to 26, wherein, The method works in a non-invasive manner to treat the tissue.

28. An ultrasonic system for dithering multiple focal points from an ultrasonic transducer, the ultrasonic system comprising: An ultrasound transducer adapted to focus ultrasound at multiple spaced focal positions, wherein the ultrasound transducer is polarized using at least a first polarization configuration and a second polarization configuration; a control module coupled to the ultrasound transducer for controlling the ultrasound transducer; and an access key configured to transmit data from a remote provider to the ultrasound system to control the functions of the ultrasound system via the control module, wherein the control module modifies the two or more focal regions through jitter of a first and a second focal region, such that the jitter moves the position of the beam focus at the two or more focal regions, wherein the jitter comprises a spaced distribution mechanically and / or electronically dispersed between the first and second focal regions via frequency oscillation; and wherein, in the case of connectivity, the access key provides system security, region-specific access to treatment guidelines, software upgrades, support for log transmission, credit transfer, and data storage.

29. The ultrasound system according to claim 28, wherein, The focal positions of the plurality of intervals are positioned in a linear sequence, and wherein the two or more focal regions are separated by intervals that jitter via the frequency swing.

30. The ultrasound system according to claim 28, wherein, The ultrasonic transducer is adapted to apply ultrasonic therapy using amplitude modulation, wherein multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity amplitudes, wherein a first amplitude is different from a second amplitude.

31. The ultrasound system according to claim 30, wherein, The ultrasonic transducer includes a piezoelectric material, and the plurality of portions of the ultrasonic transducer are adapted to generate a plurality of corresponding piezoelectric material changes in response to an electric field applied to the ultrasonic transducer.

32. The ultrasound system according to claim 31, wherein, At least one of the plurality of portions of the ultrasonic transducer is adapted to emit the ultrasonic therapy at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasonic therapy emitted by at least one portion of the piezoelectric material varies over time.

33. The ultrasonic system according to claim 32, wherein, The plurality of corresponding piezoelectric material changes include at least one of piezoelectric material expansion and piezoelectric material contraction.

34. The ultrasonic system according to any one of claims 28 to 33, wherein, The ultrasonic transducer is adapted to apply ultrasonic therapy, wherein multiple portions of the ultrasonic transducer are adapted to emit the ultrasonic therapy at multiple sound intensity phases, wherein a first phase is different from a second phase.

35. The ultrasonic system according to claim 34, wherein, The plurality of sound intensity phases include discrete phase values.

36. The ultrasonic system according to any one of claims 28 to 33, wherein, The ultrasonic transducer is adapted to: apply ultrasonic waves using amplitude modulation, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic waves at multiple sound intensity amplitudes, wherein a first amplitude is different from a second amplitude; and apply ultrasonic waves, whereby multiple portions of the ultrasonic transducer are adapted to emit ultrasonic waves at multiple sound intensity phases, wherein a first phase is different from a second phase.

37. The ultrasonic system according to any one of claims 28 to 33, wherein, The ultrasound transducer includes a moving mechanism adapted to guide ultrasound treatment in at least one pair of sequences within a separate thermo-cosmetic treatment area.

38. The ultrasonic system according to any one of claims 28 to 33, wherein, The ultrasound transducer is configured for ultrasound imaging and ultrasound therapy.

39. A method for dithering focused ultrasonic beam, the method comprising: An ultrasound probe comprising a control module and an access key for an ultrasound therapy system are provided. The access key is configured to transmit data from a remote provider to the ultrasound therapy system to control the functions of the ultrasound therapy system via the control module. During connectivity, the access key provides system security, region-specific access to treatment guidelines, software upgrades, support for log transmission, credit transfer, and data storage. The ultrasound probe is adapted to apply ultrasound therapy at two or more focal regions. The control module modifies the two or more focal regions and is coupled to the ultrasound probe, and jitters a first focal region among the two or more focal regions to change the size or position of the two or more focal regions. The jittering includes mechanically and / or electronically dispersing the spacing distribution of the two or more focal regions, and the two or more focal regions are separated by jittering intervals via frequency oscillation.

40. The method according to claim 39, wherein, The second focusing region in the two or more focusing regions is emitted from a single transducer element.

41. The method according to claim 39, further comprising imaging the focused region with an ultrasonic imaging element.

42. The method according to request item 39, wherein, The frequency modulation is in the range of 1% to 50%.

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