Systems and methods for high resolution ultrasound imaging artifact reduction

Abstract

The present disclosure relates to improving the resolution of high-speed ultrasound imaging of tissue associated with aesthetic and / or cosmetic treatment of the skin and / or tissue near the skin. In one embodiment, high resolution ultrasound imaging uses dynamic focal zone mixing to reduce the occurrence of acoustic window multipath echo artifacts. In one embodiment, high resolution ultrasound imaging reduces temporal motion artifacts using an offset between a first imaging frame in a first direction and a second imaging frame in a second direction. In some embodiments, the imaging system is used in conjunction with aesthetic and / or cosmetic skin treatments.

Description

[0001] Citation of Related Applications

[0002] This application claims priority to U.S. Provisional Application No. 63 / 476,319, filed on Dec. 20, 2022, which is hereby incorporated by reference in its entirety. Any and all priority claims identified in the Application Data Sheet or any amendment thereto are hereby incorporated by reference in accordance with the provisions of 37 CFR 1.57. Technical Field

[0003] Multiple embodiments of the present invention relate to high-resolution enhancement of high-speed motion in tissue ultrasound imaging related to aesthetic and / or cosmetic treatment of skin and / or tissue near the skin. In one embodiment, high-resolution ultrasound imaging uses dynamic focus zone mixing to reduce the occurrence of acoustic window multipath echo artifacts caused by the high frame rate and / or high-speed motion of the ultrasound imaging transducer. In one embodiment, high-resolution ultrasound imaging uses an offset between a first imaging frame in a first direction and a second imaging frame in a second direction to reduce time motion artifacts. [[ID=ll]]Background Art

[0004] Conventional ultrasound imaging typically uses a single focus zone with a fixed ultrasound imaging transducer. Summary of the Invention

[0005] For aesthetic and / or cosmetic treatment of skin and / or tissue beneath the skin, it is necessary to improve the resolution of high-speed offset ultrasound imaging using multiple focus zones to image the tissue quickly, efficiently, and accurately. In various embodiments, an ultrasound system is configured to image to visualize tissue (such as the epidermis, dermis, and / or subcutaneous layer of the tissue). In various embodiments, an ultrasound system is configured to image to visualize tissue (such as the epidermis, dermis, and / or subcutaneous layer of the tissue) to confirm the appropriate depth of a related cosmetic or medical treatment, such as to avoid certain tissues (such as nerves, bones).

[0006] In various embodiments, systems and methods for ultrasonic imaging of tissue are adapted and / or configured to image using one or more focal zones in the tissue. In one embodiment, imaging is performed using a single focal zone. In various embodiments, imaging is performed using two, three, four, or more focal zones. In various embodiments, an ultrasonic transducer for imaging is arranged to be in direct contact with tissue such as the skin surface through acoustic coupling for imaging one or more focal zones beneath the skin surface. In various embodiments, the ultrasonic transducer for imaging has an offset gap between the imaging transducer and a housing portion in an ultrasonic probe (e.g., at a window, such as a PEEK window), whereby the housing portion is arranged to be in contact with tissue such as the skin surface through acoustic coupling for imaging one or more focal zones beneath the skin surface. In some embodiments, the ultrasonic transducer for imaging has an offset gap between the imaging transducer and a housing portion that uses two or more (e.g., 2, 3, 4, 5, 6, or more) focal zones, and this offset gap can generate multipath artifacts from ultrasonic energy that bounces between the imaging transducer and (i) the acoustic window and / or (ii) the area being imaged. These artifacts can blur the clarity of the image. Systems and methods for reducing and / or eliminating such artifacts are provided in the various embodiments described herein.

[0007] In various embodiments, ultrasonic imaging is used to visualize tissue regions and / or anatomical structures. In one embodiment, ultrasonic imaging is used to confirm adequate acoustic coupling with a tissue region to improve imaging correlation between the movement of an ultrasonic imaging transducer in a first and a second direction when forming an image.

[0008] In various embodiments, ultrasonic imaging is used in combination with a cosmetic treatment or a medical treatment to visualize, plan, and / or monitor the cosmetic treatment or the medical treatment. In one embodiment, ultrasonic imaging is used in combination with applying energy to tissue. In one embodiment, ultrasonic imaging is used in combination with performing ultrasonic treatment on tissue. In one embodiment, ultrasonic imaging is used in combination with administering a dermal filler to tissue. In one embodiment, ultrasonic imaging is used in combination with administering a drug or a compound to tissue. In one embodiment, ultrasonic imaging is used in combination with administering botulinum toxin to tissue.

[0009] In various embodiments, a system and method are provided that successfully achieve aesthetic effects by splitting an ultrasound treatment beam into two, three, four, or more simultaneous focal zones to perform various therapeutic and / or imaging procedures, thereby producing visible and effective cosmetic effects via a thermal pathway using targeted and precise ultrasound. In various embodiments, an ultrasound system is configured to focus ultrasound to produce local mechanical motion within tissues and cells, either to produce local heating for tissue coagulation or to cause mechanical cell membrane rupture for non-invasive aesthetic use. In various embodiments, the ultrasound system is configured to lift the eyebrows (e.g., the eye eyebrows). In various embodiments, the ultrasound system is configured to lift loose tissues, such as submental (beneath the chin) tissues and neck tissues. 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.

[0010] In various embodiments disclosed herein, a non-invasive ultrasound system is adapted to achieve one or more of the following beneficial aesthetic and / or cosmetic improvement effects: facelift, eyebrow 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), cellulite (which may be referred to as female dysmetabolism) treatment (e.g., shallow or non-shallow female dysmetabolism), laxity improvement (e.g., upper chest), buttock lift (e.g., buttock tightening), skin tightening (e.g., treatment of laxity to cause facial or body tightening, such as the face, neck, chest, arms, legs, abdomen, buttocks, etc.), scar reduction, burn treatment, tattoo removal, vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sunspot removal, acne treatment, acne reduction.

[0011] Various embodiments are particularly advantageous because they include one, multiple, or all of the following benefits: (i) shorter imaging time, (ii) higher imaging resolution, (iii) removal of blurring artifacts from imaging, (iv) clear imaging of a moving imaging transducer, (v) more efficient imaging, and / or (vi) improved imaging to assist in related treatments or therapies.

[0012] In multiple embodiments, an ultrasonic imaging system configured to reduce imaging artifacts is provided. The ultrasonic imaging system includes: an ultrasonic probe, the ultrasonic probe including: an ultrasonic imaging transducer adapted to image a tissue region, a housing including an acoustic window, a dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies with time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance; an acoustic coupling medium within the housing configured to acoustically couple the ultrasonic imaging transducer to the acoustic window; a motion mechanism for moving the ultrasonic imaging transducer in a first direction and in a second direction, wherein when traveling in the first direction, the ultrasonic imaging transducer images in a sequence of focus zones (f1, …, f N )), where N>2, and wherein when traveling in the second direction, the ultrasonic imaging transducer images in a second sequence of focus zones (f1, ……, f N ); and a control module coupled to the ultrasonic probe to control the ultrasonic imaging transducer, wherein the control module is configured to reduce at least one multipath echo artifact by a dynamically set pulse repetition interval.

[0013] In one embodiment, the dynamically set pulse repetition interval is further configured to: measure a first offset depth; calculate a first offset time based on the first offset depth; multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and select a pulse repetition interval configured to place the at least one multipath echo artifact outside the displayed ultrasonic image.

[0014] In multiple embodiments, an ultrasonic imaging system configured to reduce imaging artifacts is provided. The ultrasonic imaging system includes: an ultrasonic probe, the ultrasonic probe including: an ultrasonic imaging transducer adapted to image a tissue region, a housing including an acoustic window, a dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies with time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance; an acoustic coupling medium within the housing configured to acoustically couple the ultrasonic imaging transducer to the acoustic window; a motion mechanism for moving the ultrasonic imaging transducer in a first direction and in a second direction, wherein when traveling in the first direction, the ultrasonic imaging transducer images in a sequence of focus zones (f1, …, f N )), where N>2, and wherein when traveling in the first direction, the ultrasonic imaging transducer images in a second sequence of focus zones (f1, ……, f N ); and a control module coupled to the ultrasonic probe to control the ultrasonic imaging transducer, wherein the control module is configured to reduce at least one multipath echo artifact by one or more dynamically set focus zone blend points.

[0015] In one embodiment, the at least one dynamically-set focus zone mixing point is further configured to: measure a first offset depth; calculate a first offset time based on the first offset depth; multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and select at least one focus zone mixing point configured to place the at least one multipath echo artifact outside the displayed ultrasound image. In one embodiment, the dynamic offset distance varies based on a change in the volume of the acoustic coupling medium, where the change in the volume of the acoustic coupling medium is a result of evaporation or leakage of the acoustic coupling medium from the housing. In one embodiment, the dynamic offset distance varies based on a change in the temperature of the acoustic coupling medium. In one embodiment, the dynamic offset distance varies based on a change in the pressure of the acoustic coupling medium. In one embodiment, the dynamic offset distance varies with the velocity of the motion mechanism in at least one of a first direction and a second direction. In one embodiment, the apparatus further includes a treatment transducer configured to perform ultrasound treatment on tissue. In one embodiment, N is any value of 2, 3, or 4.

[0016] In various embodiments, there is provided an ultrasound imaging system configured to reduce imaging artifacts, the ultrasound imaging system including: an ultrasound probe including: an ultrasound imaging transducer adapted to image a tissue region, a housing including an acoustic window, a dynamic offset distance between the ultrasound imaging transducer and the acoustic window, where the dynamic offset distance varies over time, where the dynamic offset distance includes a first offset distance and a second offset distance, where the first offset distance is different from the second offset distance; means for moving the ultrasound imaging transducer in a first direction and in a second direction; and a control module coupled to the ultrasound probe to control the ultrasound imaging transducer, where the control module is configured to reduce at least one multipath echo artifact by a dynamically-set pulse repetition interval.

[0017] In various embodiments, there is provided an ultrasound imaging module configured to reduce imaging artifacts, the ultrasound imaging module including: an ultrasound imaging transducer adapted to image a tissue region, a housing including an acoustic window, a dynamic offset distance between the ultrasound imaging transducer and the acoustic window, where the dynamic offset distance varies over time, where the dynamic offset distance includes a first offset distance and a second offset distance, where the first offset distance is different from the second offset distance; means for moving the ultrasound imaging transducer in a first direction and in a second direction; and a control module coupled to the ultrasound probe to control the ultrasound imaging transducer, where the control module is configured to reduce at least one multipath echo artifact by a dynamically-set pulse repetition interval.

[0018] In one embodiment, the at least one dynamically-set focus zone mixing point is further configured to: measure a first offset depth; calculate a first offset time based on the first offset depth; multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and select at least one focus zone mixing point configured to place the at least one multipath echo artifact outside of the displayed ultrasound image.

[0019] In various embodiments, an ultrasound imaging device configured to reduce imaging artifacts is provided. The ultrasound imaging device includes: an ultrasound module that includes: an ultrasound imaging transducer adapted to image a tissue region, a housing including an acoustic window, a dynamic offset distance between the ultrasound imaging transducer and the acoustic window, where the dynamic offset distance varies over time, where the dynamic offset distance includes a first offset distance and a second offset distance, where the first offset distance is different from the second offset distance; means for moving the ultrasound imaging transducer in a first direction and in a second direction; and a control module coupled to the ultrasound probe to control the ultrasound imaging transducer, where the control module is configured to reduce at least one multipath echo artifact by a dynamically-set pulse repetition interval.

[0020] In one embodiment, the at least one dynamically-set focus zone mixing point is further configured to: measure a first offset depth; calculate a first offset time based on the first offset depth; multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and select at least one focus zone mixing point configured to place the at least one multipath echo artifact outside of the generated ultrasound image. In one embodiment, the dynamic offset distance varies based on a change in the volume of the acoustic coupling medium, where the change in the volume of the acoustic coupling medium is the result of evaporation or leakage of the acoustic coupling medium from the housing. In one embodiment, the dynamic offset distance varies based on a change in the temperature of the acoustic coupling medium. In one embodiment, the dynamic offset distance varies based on a change in the pressure of the acoustic coupling medium. In one embodiment, the dynamic offset distance varies with the velocity of the mechanism in at least one of the first and second directions. In one embodiment, the device further includes a treatment transducer configured to apply ultrasound treatment to the tissue. In one embodiment, N is any one of the values 2, 3, or 4.

[0021] In multiple embodiments, a method for reducing multipath echo artifacts in an ultrasound image is provided. The method includes: providing an ultrasound probe that includes: an ultrasound imaging transducer adapted to image a tissue region, a housing including an acoustic window, a dynamic offset distance between the ultrasound imaging transducer and the acoustic window, wherein the dynamic offset distance varies over time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance; an acoustic coupling medium within the housing configured to acoustically couple the ultrasound imaging transducer to the acoustic window; a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction, wherein when traveling in the first direction, the ultrasound imaging transducer images in a sequence of focus zones (f1, …, f N ) where N>2, and wherein when traveling in the second direction, the ultrasound imaging transducer images in a second sequence of focus zones (f1, ……, f N ) while traveling in the second direction; and measuring a first offset depth; calculating a first offset time based on the first offset depth; multiplying the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and selecting a pulse repetition interval configured to place the at least one multipath echo artifact outside the displayed ultrasound image.

[0022] In multiple embodiments, a method for reducing multipath echo artifacts in an ultrasound image is provided. The method includes: providing an ultrasound probe that includes: an ultrasound imaging transducer adapted to image a tissue region, a housing including an acoustic window, a dynamic offset distance between the ultrasound imaging transducer and the acoustic window, wherein the dynamic offset distance varies over time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance; an acoustic coupling medium within the housing configured to acoustically couple the ultrasound imaging transducer to the acoustic window; a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction; calculating a first offset time based on the first offset depth calculation; multiplying the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and selecting at least one focus zone mixing point configured to place the at least one multipath echo artifact outside the displayed ultrasound image.

[0023] In one embodiment, the method further includes imaging the tissue and displaying the tissue. In one embodiment, the method further includes imaging the tissue and displaying the tissue without treating the tissue. In one embodiment, the method further includes treating the tissue.

[0024] In multiple embodiments, a method for improving ultrasound imaging alignment by reducing spatial and temporal motion artifacts is provided. The method includes: providing an ultrasound probe that includes: an ultrasound imaging transducer adapted to image a tissue region, a motion mechanism attached to the ultrasound imaging transducer; wherein when traveling in a first direction, the ultrasound imaging transducer generates a first image in a sequence of focus zones (f1, …, f N ) where N>2, and wherein when traveling in a second direction, the ultrasound imaging transducer generates a second image in a second sequence of focus zones (f1, ……, f N ) while traveling in the second direction; acquiring a first imaging frame; acquiring a second imaging frame; calculating an offset between the first imaging frame and the second imaging frame to determine lateral misregistration; displaying the first imaging frame; and displaying the second imaging frame, wherein the offset is applied to the second imaging frame to reduce temporal motion artifacts.

[0025] In one embodiment, the method further includes calculating an optimized image using at least one trigger offset; and applying the at least one trigger offset to subsequent image acquisitions, wherein due to the application of the at least one trigger offset, lateral misregistration is reduced.

[0026] In multiple embodiments, a method for improving ultrasound imaging alignment by reducing spatial and temporal motion artifacts is provided. The method includes: providing an ultrasound probe that includes: an ultrasound imaging transducer adapted to image a tissue region, a motion mechanism attached to the ultrasound imaging transducer; wherein when traveling in a first direction, the ultrasound imaging transducer generates a first image in a sequence of focus zones (f1, …, f N ) where N>2, and wherein when traveling in a second direction, the ultrasound imaging transducer generates a second image in a second sequence of focus zones (f1, ……, f N ) while traveling in the second direction; acquiring a plurality (N>1) of imaging frames; calculating a temporal average of at least two imaging frames; and displaying the temporal average of the at least two imaging frames to reduce temporal motion artifacts.

[0027] In one embodiment, the method further includes calculating an optimized image using at least one trigger offset; and applying the at least one trigger offset to subsequent image acquisitions, wherein averaging of N>1 consecutive imaging frames is enabled when the spatial misregistration between the current and previously acquired imaging frames is less than a predetermined threshold.

[0028] In multiple embodiments, a method for improving ultrasound imaging alignment by reducing spatial and temporal motion artifacts is provided. The method includes: providing an ultrasound probe, the ultrasound probe including: an ultrasound imaging transducer adapted to image a tissue region, a motion mechanism attached to the ultrasound imaging transducer; wherein when traveling in a first direction, the ultrasound imaging transducer generates a first image in a sequence of focus zones (f1, …, f N ) where N>2, and wherein when traveling in a second direction, the ultrasound imaging transducer generates a second image in a second sequence of focus zones (f1, ……, f N ) while traveling in the second direction; acquiring a first imaging frame; acquiring a second imaging frame; calculating an offset between the first imaging frame and the second imaging frame to determine lateral misregistration; calculating a temporal average of the first imaging frame and the second imaging frame; and displaying the temporal average of the first imaging frame and the offset relative to the second imaging frame to reduce spatial and temporal motion artifacts.

[0029] In one embodiment, the method further includes calculating an optimized image using at least one trigger offset; and applying the at least one trigger offset to the optimized image, wherein due to the application of the at least one trigger offset, lateral misregistration is reduced. In one embodiment, the method further includes imaging the tissue and displaying the tissue. In one embodiment, the method further includes imaging the tissue and displaying the tissue without treating the tissue. In one embodiment, the method further includes treating the tissue.

[0030] In multiple embodiments, an ultrasound imaging system configured to reduce imaging misalignment is provided. The ultrasound imaging system includes: an ultrasound probe, the ultrasound probe including an ultrasound treatment transducer adapted to apply ultrasound treatment to tissue, an ultrasound imaging transducer adapted to image the tissue, and a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction, wherein the ultrasound imaging transducer is mechanically attached to the motion mechanism, wherein the first direction is opposite to the second direction, and wherein when traveling in the first direction, the ultrasound imaging transducer images in a sequence of focus zones (f1, …, f N ) where N>1, and wherein when traveling in the second direction, the ultrasound imaging transducer images in a second sequence of focus zones (f1, ……, f N ), wherein spatial registration between imaging in the first direction and imaging in the second direction is improved by staggering trigger positions, and wherein the ultrasound imaging system employs direction-dependent focus zone sorting (f1, ……, f N ) and (f1, ……, f N ) on consecutive A-lines; and a control module coupled to the ultrasound probe to control the ultrasound imaging transducer.

[0031] In one embodiment, N = any value in the group consisting of 2, 4, 6, and 8. In one embodiment, the first movement direction of the transducer is any one or more directions in the group consisting of linear, rotational, and curvilinear; wherein the second direction is the reverse path of the first direction. In one embodiment, the ultrasound treatment is at least one of the following treatments: facelift, brow lift, chin lift, eye treatment, wrinkle reduction, improvement of relaxation, buttock lift, scar reduction, burn treatment, skin tightening, blood vessel reduction, sweat gland treatment, sunspot removal, fat treatment, cellulite treatment, vaginal tightening, acne treatment, and abdominal relaxation treatment.

[0032] The methods summarized above and elaborated further below describe certain actions taken by a practitioner; however, it should be understood that they may also include instructions given by another party for these actions. Thus, for example, the action of "moving the imaging transducer" includes "instructing the movement of the imaging transducer".

[0033] In some embodiments, the system includes various features that exist as a single feature (as opposed to multiple features). Multiple features or components are provided in alternative embodiments. In various embodiments, the system includes one, two, three, or more embodiments of any feature or component disclosed herein, or consists essentially of these embodiments, or consists of these embodiments. In some embodiments, a certain feature or component is not included, and that feature or component can be cancelled from a particular claim such that the system does not have such a feature or component. In some embodiments, steps are not required when performing the method. In some embodiments, the system does not include a certain component. Additionally, the application area will become apparent by reading the description provided herein. It should be understood that the description and specific examples are for illustrative purposes only and are not intended to limit the scope of the embodiments disclosed herein. BRIEF DESCRIPTION OF THE DRAWINGS

[0034] The drawings described herein are for illustrative purposes only and are not intended to limit the scope of the present disclosure in any way. The embodiments can be more fully understood by reading the detailed description and the drawings. In multiple embodiments, the features in one drawing are applicable to other drawings.

[0035] Figure 1A is a schematic diagram of an ultrasound system according to various embodiments;

[0036] Figure 1B is a schematic diagram of an ultrasound system according to various embodiments;

[0037] Figure 1C is a schematic diagram of an ultrasound system according to various embodiments;

[0038] Figure 2Schematic diagram of an ultrasound system coupled to a region of interest according to various embodiments;

[0039] Figure 3 Schematic diagram of an imaging diagnostic ultrasound system according to various embodiments;

[0040] Figure 4 Schematic diagram of bidirectional imaging at the same lateral position according to various embodiments;

[0041] Figure 5 Schematic diagram of direction - related focus zone sorting according to various embodiments;

[0042] Figure 6 Schematic diagram of direction - related focus zone sorting with different trigger positions according to various embodiments;

[0043] Figure 7 Schematic diagram of direction - related focus zone sorting on consecutive A - lines according to various embodiments;

[0044] Figure 8A and 8B Graph and schematic image showing the generation of multipath echo artifacts over time according to various embodiments;

[0045] Figure 9A and 9B Graph and schematic image showing the reduction or elimination of multipath echo artifacts using a static waiting time according to various embodiments;

[0046] Figure 10A and 10B Graph and schematic image showing the generation of multipath echo artifacts with a dynamic or varying offset gap according to various embodiments;

[0047] Figure 11 Shows a method for reducing or eliminating artifacts in a dynamically varying offset over time according to various embodiments;

[0048] Figure 12A Schematic diagram of multi - focus zone imaging that generates artifacts in one or more focus zones according to one embodiment;

[0049] Figure 12B Schematic diagram of a display of multi - hybrid focus zone imaging that reduces or eliminates artifacts in one or more focus zones according to one embodiment;

[0050] Figure 13 Shows a method for determining an ingress image trigger offset to improve lateral imaging registration according to various embodiments;

[0051] Figure 14 Shows a captured image of unstable pixel jitter according to various embodiments;

[0052] Figure 15A Shows quantization time motion artifacts with a major lateral shift according to various embodiments;

[0053] Figure 15B Shows quantization time motion artifacts that are temporally stable according to various embodiments;

[0054] Figure 15C Shows quantization time motion artifacts that are depth consistent according to various embodiments;

[0055] Figure 16A Shows a captured image of unstable pixels with lateral jitter according to various embodiments;

[0056] Figure 16B Shows a captured image of stabilizing an image using a shift filter according to various embodiments;

[0057] Figure 17A Shows a captured image of unstable pixels with vertical jitter according to various embodiments;

[0058] Figure 17B Shows a captured image using a temporal averaging of consecutive frame filter according to various embodiments;

[0059] Figure 18A Shows a captured image of unstable pixel jitter according to various embodiments;

[0060] Figure 18B Shows a captured image using shift data and a temporal averaging of consecutive frame filter according to various embodiments;

[0061] Figure 19 Is a schematic diagram showing the correlation coefficient calculated over time according to various embodiments;

[0062] Figure 20 Is a schematic diagram showing frame-by-frame motion detection according to various embodiments;

[0063] Figure 21 Is a schematic diagram showing the correlation coefficient calculated over time according to various embodiments;

[0064] Figure 22A Shows a captured image of unstable pixel jitter according to various embodiments;

[0065] Figure 22B Is a captured image using shift data and a temporal averaging of consecutive frame filter when no motion is detected according to various embodiments. Detailed Implementation Modes

[0066] The following description sets forth examples of implementation modes and is not intended to limit the invention or its teachings, applications, or uses. It should be understood that in all the figures, corresponding reference numerals indicate like or corresponding components and features. The description of specific embodiments shown in the various implementation modes is for illustrative purposes only and is not intended to limit the scope of the invention disclosed herein. Additionally, the recitation of multiple implementation modes having the stated features is not intended to exclude other implementation modes having additional features or other implementation modes combining different combinations of the stated features. Moreover, features in one implementation mode (e.g., one figure) may be combined with the description (and figures) of other implementation modes.

[0067] In various implementation modes, systems and methods for ultrasonic imaging of tissue are adapted to and / or configured to image using one or more focal zones in the tissue. In one implementation mode, imaging is performed using a single focal zone. In various implementation modes, imaging is performed using two, three, four, or more focal zones. In various implementation modes, an ultrasonic transducer for imaging is arranged to be in direct contact with tissue such as the skin surface through acoustic coupling for imaging one or more focal zones beneath the skin surface. In various implementation modes, the ultrasonic transducer for imaging has an offset gap between the imaging transducer and a housing portion in an ultrasonic probe (e.g., at an acoustic window, such as a PEEK window), whereby the housing portion is arranged to be in contact with tissue such as the skin surface through acoustic coupling for imaging one or more focal zones beneath the skin surface. In some implementation modes, the ultrasonic transducer for imaging has an offset gap between the imaging transducer and a housing portion using two or more (e.g., 2, 3, 4, 5, 6, or more) focal zones, and this offset gap generates multipath artifacts from ultrasonic energy that bounces between the imaging transducer and (i) the acoustic window and / or (ii) the region being imaged. These artifacts may blur the clarity of the imaging. Systems and methods for reducing and / or eliminating such artifacts are provided in the various implementation modes described herein. In some implementation modes, the imaging is stationary (e.g., at least a part of the tissue and / or the device does not move). In some implementation modes, the imaging is in motion (e.g., at least a part of the tissue and / or the device moves).

[0068] In various implementation modes, ultrasonic imaging is used to visualize tissue regions and / or anatomical structures. In one implementation mode, ultrasonic imaging is used to confirm sufficient acoustic coupling with a tissue region to improve imaging correlation between the movement of an ultrasonic imaging transducer in a first and a second direction when forming an image.

[0069] In various embodiments, ultrasound imaging is used in combination with cosmetic or medical treatment to visualize, plan, and / or monitor cosmetic or medical treatment. In one embodiment, ultrasound imaging is used in combination with applying energy to tissue. In one embodiment, ultrasound imaging is used in combination with performing ultrasound treatment on tissue. In one embodiment, ultrasound imaging is used in combination with administering a dermal filler to tissue. In one embodiment, ultrasound imaging is used in combination with administering a drug or compound to tissue. In one embodiment, ultrasound imaging is used in combination with administering botulinum toxin to tissue.

[0070] In various embodiments, systems and methods for ultrasonic treatment of tissue are adapted and / or configured to provide cosmetic treatment. In some embodiments, an apparatus and method are provided for directing ultrasonic treatment to a single focus or multiple simultaneous foci. In various embodiments, ultrasonic imaging is used to confirm adequate acoustic coupling with the treatment area to improve performance or improve the correlation between movement in a first direction and a second direction when forming an image during a cosmetic and / or medical procedure. In some embodiments, an apparatus and method are provided that use ultrasonic imaging to confirm adequate acoustic coupling with the treatment area to improve performance and safety when directing ultrasonic treatment to a single focus or multiple simultaneous foci during a cosmetic and / or medical procedure. In some embodiments, improved ultrasonic imaging apparatus and methods provide better correlation between movement in a first direction and a second direction when forming an image. Embodiments of the present invention provide better imaging correlation between a first movement direction and a second movement direction (e.g., better correlation between images formed by left-to-right and right-to-left movement). Embodiments of the present invention provide better spatial registration between a first movement direction and a second movement direction (e.g., better correlation between images formed by left-to-right and right-to-left movement). Improved ultrasonic imaging apparatus and methods improve the effectiveness of faster A-line and / or B-mode imaging (e.g., 1.5 times, 2 times, 3 times, 5 times the scan rate). In various embodiments, ultrasonic energy is used to non-invasively treat tissue beneath or even at the skin surface, such as the epidermis, dermis, fascia, muscle, fat, and superficial musculoaponeurotic system ("SMAS"). The ultrasonic energy can be focused at one or more treatment points and / or regions, can be unfocused and / or defocused, and can be applied to an area of interest that includes at least one of the epidermis, dermis, hypodermis, fascia, muscle, fat, cellulite, and SMAS to achieve cosmetic and / or therapeutic effects. In various embodiments, the system and / or method provides non-invasive dermatological treatment to tissue by thermotherapy, coagulation, ablation, and / or tightening. In multiple embodiments disclosed herein, non-invasive ultrasound is used to achieve one or more of the following effects: facelift, 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), cellulite treatment (e.g., mild or non-mild female lipodystrophy), improvement of laxity (e.g., upper chest), buttock lift (e.g., buttock tightening), treatment of skin laxity (e.g., tissue treatment for tightening or abdominal laxity treatment), scar reduction, burn treatment, tattoo removal, vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sunspot removal, acne treatment, and acne scar removal. In one embodiment, fat reduction is achieved.In various embodiments, for example, compared to untreated tissue, a reduction in cellulite (e.g., shallow or non-shallow dimpling female lipodystrophy) of about 10 - 20%, 20 - 40%, 40 - 60%, 60 - 80% or higher (and overlapping ranges therein) or an improvement in one or more features (e.g., shallow dimples, nodules, "orange peel" appearance, etc.) is achieved. In one embodiment, laxity is treated. In some embodiments, two, three or more beneficial effects are achieved during the same treatment session and can be achieved simultaneously.

[0071] Various embodiments relate to a device or method for controlling the delivery of energy to tissue. In various embodiments, various forms of energy can include acoustic energy, ultrasonic energy, light energy, laser energy, radio frequency (RF) energy, microwave energy, electromagnetic energy, radiant energy, thermal energy, cryogenic energy, electron beam energy, photon-based energy, magnetic energy, magnetic resonance energy, and / or other forms of energy. Various embodiments relate to a device or method for splitting an ultrasonic energy beam into multiple energy beams. In various embodiments, a device or method can be used to vary the delivery of ultrasonic energy in any process, such as but not limited to therapeutic ultrasound, diagnostic ultrasound, ultrasonic welding, any application involving coupling mechanical waves to an object, and other processes. Generally, for therapeutic ultrasound, tissue effects are achieved by focusing acoustic energy from an aperture using focusing techniques. In certain 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 can be referred to as the generation of a thermal coagulation point (TCP). In some embodiments, a region can include a point. In some embodiments, the region is a line, plane, sphere, ellipsoid, cube, or other one-dimensional, two-dimensional, or three-dimensional shape. It is through the generation of TCP at specific locations that thermal and / or mechanical ablation of tissue can occur non-invasively or remotely. In some embodiments, ultrasonic treatment does not include cavitation and / or shock waves. In some embodiments, ultrasonic treatment includes cavitation and / or shock waves.

[0072] In one embodiment, TCPs can be generated in a linear or substantially linear, curved or substantially curved region or sequence, with each individual TCP separated from an adjacent TCP by a treatment spacing. In one embodiment, multiple TCP sequences can be generated in a treatment area. For example, TCPs can be formed along a first sequence and a second sequence spaced apart from the first sequence by a treatment distance. Although ultrasonic treatment can be performed by generating individual TCPs in one or more TCP sequences, it may be desirable to reduce the treatment time and the corresponding risk of pain and / or discomfort felt by the patient. The treatment time can be reduced by forming multiple TCPs simultaneously, almost simultaneously, or sequentially. In some embodiments, by generating multiple TCPs, the treatment time can be reduced by 10%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, 80% or more.

[0073] Various embodiments address potential challenges posed by the performance of ultrasonic treatment. In various embodiments, the time to form TCPs at a target tissue for a desired cosmetic and / or therapeutic clinical method is reduced. In various embodiments, the target tissue is, but not limited to, any one of skin, eyelids, eyelashes, eyebrows, caruncles, 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 laxity), stomach, liver, kidneys, uterus, breasts, vagina, prostate, testicles, glands, thyroid, viscera, hair, muscle, bone, ligaments, cartilage, fat, adipose sacs, adipose tissue, subcutaneous tissue, implanted tissue, implanted organs, lymph, tumors, cysts, abscesses, or a portion of a nerve, or any combination thereof.

[0074] Various embodiments of an ultrasound treatment and / or imaging device are described in U.S. application Ser. No. 12 / 996,616, published as U.S. Publication No. 2011-0112405 A1 on May 12, 2011, which is the U.S. national stage application under 35 U.S.C. § 371 of International Application PCT / US2009 / 046475, filed on Jun. 5, 2009 and published in English on Dec. 10, 2009. Various embodiments of an ultrasound treatment and / or imaging device are described in U.S. application Ser. No. 14 / 193,234, published as U.S. Publication No. 2014 / 0257145 on Sep. 11, 2014, which is incorporated herein by reference in its entirety. Various embodiments of an ultrasound treatment and / or imaging device are described in International Application PCT / US17 / 46703, published as WO 2018 / 035012 on Feb. 22, 2018, which has a U.S. national stage application Ser. No. 15 / 562,384, published as U.S. Publication No. 2019 / 0142380 on May 16, 2019, each of which is incorporated herein by reference in its entirety. Various embodiments of an ultrasound treatment and / or imaging device are described in International Application PCT / US19 / 14617, published as WO 2019 / 147596 on Aug. 1, 2019, which has a U.S. national stage application Ser. No. 16 / 964,914, published as U.S. Publication No. 2021 / 0038925 on Feb. 11, 2021, each of which is incorporated herein by reference in its entirety.

[0075] System Overview

[0076] Please refer to Figure 1A 、 1BAs shown in the illustration in 1C, various embodiments of the ultrasound system 20 include a hand wand (e.g., a handheld unit) 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., WIFI, Bluetooth, a modem, etc.) for communicating with another party, a manufacturer, a supplier, a service provider, the Internet, and / or the cloud. In some embodiments, a cart 301 provides mobility and / or positioning of the system 20, and may include wheels, a surface for writing or placing components, and / or compartments 302 (e.g., drawers, containers, shelves, etc.) for storing or organizing components. In some embodiments, the cart has a power source, such as an electrical connection to a battery and / or one or more wires for connecting power and communication (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 hand wand 100 may be coupled to the controller 300 through an interface 130, which may be a wired or wireless interface. The interface 130 may be coupled to the hand wand 100 through a connector 145. The distal end of the interface 130 may be connected to a controller connector on a circuit 345 (not shown). In one embodiment, the interface 130 may deliver controllable power from the controller 300 to the hand wand 100. In one embodiment, the system 20 has multiple imaging channels (e.g., 2, 4, 6, 8, 10 channels) for ultra-clear HD (high definition) visualization of subcutaneous structures to improve imaging. In one embodiment, the system 20 has multiple treatment channels (e.g., 2, 4, 6, 8, 10 channels) and a precision linear drive motor that doubles treatment accuracy while increasing speed (e.g., increasing by 25%, 40%, 50%, 60%, 75%, 100% or more).

[0077] In various embodiments, the controller 300 can be adapted and / or configured to operate in conjunction with the handpiece 100 and the module 200 and the functions of the entire ultrasound system 20. In various embodiments, multiple controllers 300, 300', 300", etc. can be adapted to and / or configured to operate in conjunction with multiple handpieces 100, 100', 100", etc. and / or multiple modules 200, 200', 200", etc. The controller 300 can include a connection to one or more interactive graphic displays 310, which can include a touchscreen monitor and a graphical user interface (GUI) that allows a user to interact with the ultrasound system 20. In one embodiment, a second, smaller, more mobile display allows the user to more easily arrange and view the treatment screen. In one embodiment, the second display allows the system user to view the treatment screen (e.g., on a wall, mobile device, large screen, remote screen). In one embodiment, the graphic 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, a system and apparatus for controlling the multiplexing of electronics and / or mechanical scanning and / or transducer modules, a system for power delivery, a system for monitoring, a system for sensing the spatial position of the probe and / or transducer and / or the multiplexing of transducer modules, and / or a system 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 logics, such as one or more of a microcontroller, a microprocessor, a field programmable gate array, a computer board, and associated components, including firmware and control software, which can interface with user control and interface circuits and input / output circuits and systems for communication, display, interface, 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 to achieve user-defined treatment goals. In addition, the controller 300 can include various input / output modules, such as switches, buttons, etc., which can also be adapted to and / or configured to control the operation of the ultrasound system 20.

[0078] In one embodiment, the handpiece 100 includes one or more finger-activated controllers or switches, such as 150 and 160. In various embodiments, one or more thermotherapy controllers 160 (such as switches, buttons) activate and / or stop the treatment. In various embodiments, one or more imaging controllers 150 (such as switches, buttons) activate and / or stop the imaging. In one embodiment, the handpiece 100 may include a removable module 200. In other embodiments, the module 200 may be non-removable. In various embodiments, the module 200 may be mechanically coupled to the handpiece 100 using a latch or coupler 140. In various embodiments, one or more interface guides 235 may be used to assist in coupling the module 200 to the handpiece 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. In one embodiment, the module 200 includes a bubble collector to reduce bubbles in the acoustic medium. The handpiece 100 may include a pure imaging module, a pure treatment module, an imaging and treatment module, etc. In various embodiments, the ultrasonic transducer 280 is capable of moving in one or more directions 290 within the module 200. In some embodiments, the transducer 280 is connected to a motion mechanism 400. In some embodiments, the transducer 280 is not connected to the motion mechanism 400. In various embodiments, the motion mechanism includes zero, one or more bearings, shafts, rods, screws, lead screws 401, encoders 402 (such as optical encoders for measuring the position of the transducer 280), motors 403 (such as stepper motors) to help ensure precise and repeatable movement of the transducer 280 within the module 200. In various embodiments, the module 200 may include a transducer 280 capable of emitting energy through an acoustic transmission member 230. In one embodiment, the module 200 has an offset distance 210 between the transducer 280 and the acoustic transmission member 230. In one embodiment, the module 200 has an offset distance 211 between the transducer 280 and the bottom of the imaging area distance. In one embodiment, the control module 300 may be coupled to the handpiece 100 via an interface 130, and the graphical user interface 310 is adapted and / or configured to control the module 200. In one embodiment, the control module 300 is capable of powering the handpiece 100. In one embodiment, the handpiece 100 may include a power source. In one embodiment, the switch 150 is adapted and / or configured to control the tissue imaging function, and the switch 160 is adapted and / or configured to control the tissue treatment function. In various embodiments, through the controlled operation of the control system 300 of the transducer 280, the delivery of the transmitted energy 50 is provided by the module 200 at an appropriate focal depth, distribution, timing, and energy level to achieve the desired treatment effect of the thermal coagulation zone 550.

[0079] In one embodiment, module 200 can be coupled to the handpiece 100. Module 200 can transmit and receive energy, such as ultrasonic energy. Module 200 can be electrically coupled to the handpiece 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 module 200 and handpiece 100. Module 200 can include various probe and / or transducer configurations. For example, module 200 can be adapted and / or configured for a combined dual-mode imaging / therapy transducer, coupled or co-packaged imaging / therapy transducers, separate therapy and imaging probes, etc. In one embodiment, when module 200 is inserted into handpiece 100 or connected to handpiece 100, the controller 300 automatically detects it and updates the interactive graphical display 310.

[0080] In some embodiments, an access key 320 (such as a secure USB drive, key) is removably connected to the system 20 to allow the system 20 to operate. In various embodiments, the access key is programmed to be specific to the customer and provides multiple functions, including system security, country / region-specific access to treatment guidelines and functions, software upgrades, support log transfer and / or credit transfer and / or storage. In various embodiments, the system 20 has an Internet and / or data connection. In one embodiment, the connection provides a method for transferring data between the system 20 provider and the customer. In various embodiments, the data includes credit, software updates, and support logs. Based on the specific way the user's console is connected to the Internet, the connection is divided into different model embodiments. In one embodiment, the disconnected model connection includes a console that is disconnected from the Internet and the customer has no Internet access. Credit transfer and software upgrades are performed by sending the access key (such as a USB drive) to the customer. In one embodiment, the semi-connected model connection includes a console that is disconnected from the Internet but the customer has Internet access. The customer's personal computer, smartphone, or other computing device is used in combination with the system access key for credit transfer, software upgrades, and support log transfer to enable data transfer. In one embodiment, the fully connected model connection includes a console that is wirelessly connected to the Internet using WIFI, cellular modem, Bluetooth, or other protocols. Credit transfer, software upgrades, and support log transfer are performed directly between the console and the cloud. In various embodiments, the system 20 is connected to an online portal for streamlined and / or automated inventory management, on-demand treatment purchase, and business analytics insights, thereby advancing the customer's beauty treatment business to the next level.

[0081] In various embodiments, ultrasound energy is used to non-invasively treat tissue beneath the skin surface or even at the skin surface, such as the epidermis, dermis, hypodermis, fascia, 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 is applied to a region of interest that includes at least one of the epidermis, dermis, hypodermis, fascia, and SMAS to achieve a therapeutic effect. Figure 2 is a schematic diagram of an ultrasound system 20 coupled to a region of interest 10. In various embodiments, the tissue layer of the region of interest 10 can be located at any part of the subject's body. In one embodiment, the tissue layer is located in the head and facial region of the subject. A cross-sectional portion of the tissue of the region of interest 10 includes a skin surface 501, an epidermis layer 502, a dermis layer 503, a fat layer 505, a superficial musculoaponeurotic system 507 (hereinafter referred to as “SMAS 507”), and a muscle layer 509. The tissue may also include a hypodermis 504, which may include any tissue beneath the dermis layer 503. The combination of these layers may be collectively referred to as subcutaneous tissue 510. In Figure 2 a treatment area 525 located beneath the surface 501 is also shown. In one embodiment, the surface 501 may be the skin surface of the subject 500. Although embodiments involving treatment at tissue layers are 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 for tissues (including but not limited to one or a combination of muscle, fascia, SMAS, dermis, epidermis, fat, fat cells, cellulite (which may be referred to as female adiposis dysregulation, such as non-pitting female adiposis dysregulation), collagen, skin, blood vessels) at the face, neck, head, arm, leg, or any other location on or in the body (including body cavities). In various embodiments, the reduction in cellulite (such as non-pitting female adiposis dysregulation) reaches 2%, 5%, 10%, 15%, 20%, 25%, 30%, 40%, 50%, 75%, 80%, 90%, 95%, and any range therebetween.

[0082] Please refer to Figure 2In the illustrated embodiment, an embodiment of the ultrasound system 20 includes a handpiece 100, a module 200, and a controller 300. In one embodiment, the module 200 includes a transducer 280. In one embodiment, the ultrasound system 20 having the transducer 280 is adapted and / or configured to treat tissue at a focal depth 278. In one embodiment, the focal depth 278 is the distance between the transducer 280 and the target tissue to be treated. In one embodiment, for a given transducer 280, the focal depth 278 is fixed. In one embodiment, for a given transducer 280, the focal depth 278 is variable. In one embodiment, the transducer 280 is configured to treat simultaneously at multiple depths (e.g., 1.5 mm, 3.0 mm, 4.5 mm, or other depths) under the skin surface.

[0083] In one embodiment, the module 200 may include a transducer 280 capable of emitting energy through an acoustic transmission member 230. In various embodiments, the depth may refer to the focal depth 278. In one embodiment, the transducer 280 may have an offset distance 270, which is the distance between the transducer 280 and the surface of the acoustic transmission member 230. In one embodiment, the focal depth 278 of the transducer 280 is a fixed distance from the transducer. In one embodiment, the transducer 280 may have a fixed offset distance 270 from the transducer to the acoustic transmission member 230. In one embodiment, the acoustic transmission member 230 is adapted and / or configured to contact the skin surface 501 at a location on the module 200 or the ultrasound system 20. In various embodiments, the amount by which the focal depth 278 exceeds the offset distance 270 corresponds to treatment at a target area at a tissue depth 279 under the 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 acoustic transmission member 230 and the target area, which is measured in terms of the distance from the surface portion of the handpiece 100 or the module 200 that contacts the skin (with or without an acoustic coupling gel, medium, etc.) and the tissue depth from the skin surface contact point to the target area. In one embodiment, the focal depth 278 may correspond to the sum of the offset distance 270 (measured to the surface of the acoustic transmission member 230 that contacts the coupling medium and / or the skin 501) and the tissue depth 279 under the skin surface 501 to the target area. In various embodiments, the acoustic transmission member 230 is an acoustic window, such as a PEEK window, configured to transmit ultrasonic waves to the outside of the acoustic transmission member 230 through one or more coupling media within the module 200.

[0084] The coupling component can include a variety of substances, materials, and / or devices to facilitate coupling the transducer 280 or the module 200 to the region of interest. For example, the coupling component can include an acoustic coupling system adapted for and / or configured for acoustic coupling of ultrasonic energy and signals. An acoustic coupling system with possible connections such as a manifold can be used to couple sound to the region of interest, providing focusing with a lens filled with a liquid or fluid. The coupling system can facilitate such coupling by using one or more coupling media, which include air, gas, water, liquid, fluid, gel, solid, non-gel, and / or any combination thereof, or any other medium that allows signals to be transmitted between the transducer 280 and the region of interest. In one embodiment, one or more coupling media are provided within the transducer. In one embodiment, the fluid-filled module 200 contains one or more coupling media within a housing. In one embodiment, the fluid-filled module 200 contains one or more coupling media within a sealed housing that can be separated 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%, more than 99%, more than 98%, more than 95%, more than 90%, more than 80%, more than 75%, more than 60%, more than 50%, more than 40%, more than 30%, more than 25%, more than 20%, more than 10%, and / or more than 5%.

[0085] In various embodiments, the transducer 280 can image and treat regions of interest located at any suitable tissue depth 279. In one embodiment, the acoustic power that the transducer module 280 can provide is in the range of less than about 1W, from about 1W to about 100W, or greater than about 100W, such as 200W, 300W, 400W, 500W. In one embodiment, the transducer module 280 can provide acoustic power at frequencies of less than about 1MHz, from about 1MHz to about 10MHz (such as 3MHz, 4MHz, 4.5MHz, 7MHz, 10MHz), and greater than about 10MHz. In one embodiment, the module 200 has a focal depth 278 for treating at a tissue depth 279 of about 4.5mm below the skin surface 501. In one embodiment, the module 200 has a focal depth 278 for treating at a tissue depth 279 of about 3mm below the skin surface 501. In one embodiment, the module 200 has a focal depth 278 for treating at a tissue depth 279 of about 1.5mm below the skin surface 501. Some non-limiting embodiments of the transducer 280 or the module 200 can be adapted and / or configured to deliver ultrasonic energy at tissue depths such as 1.5mm, 3mm, 4.5mm, 6mm, 7mm, less than 3mm, 3mm to 4.5mm, 4.5mm to 6mm, greater than 4.5mm, greater than 6mm, etc., and within ranges such as 0-3mm, 0-4.5mm, 0-6mm, 0-25mm, 0-100mm, etc., and at any depth therein. In one embodiment, the ultrasound system 20 is provided with two or more transducer modules 280. For example, a first transducer module can apply treatment at a first tissue depth (such as 4.5mm), a second transducer module can apply treatment at a second tissue depth (such as 3mm), and a third transducer module can apply treatment at a third tissue depth (such as 1.5-2mm). In one embodiment, at least some or all of the transducer modules can be adapted and / or configured to apply treatment at substantially the same depth.

[0086] In various embodiments, it may be advantageous to vary the number of focal positions (e.g., having a tissue depth 279) of an ultrasound procedure, because even though the focal depth 278 of transducer 270 is fixed, it allows treating a patient at varying tissue depths. This can provide a synergistic effect and maximize the clinical efficacy of a single treatment procedure. For example, treating at multiple depths under a single surface area allows for a greater total tissue treatment volume, which results in enhanced collagen formation and tightening. Additionally, treating at different depths affects different types of tissue, resulting in different clinical effects that together provide an enhanced overall cosmetic effect. For example, surface treatment can reduce the visibility of wrinkles, while deeper treatment can induce the formation of more collagen growth. Similarly, treating at different locations at the same or different depths can improve treatment.

[0087] While in some embodiments it may be advantageous to treat an object at different locations during a single procedure, in other embodiments it may be beneficial to treat sequentially over time. For example, an object can be treated at one depth at a first time under the same surface area and at a second depth at a second time, and so on. In various embodiments, the time can be on the order of nanoseconds, microseconds, milliseconds, seconds, minutes, hours, days, weeks, months, or other time periods. New collagen produced by the first treatment may be more sensitive to subsequent treatments, which may be desirable for certain indications. Alternatively, it may be advantageous to treat at multiple depths under the same surface area during a single procedure, because treatment at one depth can synergistically enhance or complement treatment at another depth (e.g., due to enhanced blood flow, stimulation of growth factors, hormonal stimulation, etc.). In multiple embodiments, different transducer modules provide treatment at different depths. In one embodiment, a single transducer module can be adjusted or controlled for different depths. Safety features that minimize the risk of selecting an incorrect depth can be used in conjunction with a single-module system.

[0088] In multiple embodiments, a method for treating the lower face and neck regions (such as the submental region) is provided. In multiple embodiments, a method for treating (such as softening) the mentolabial fold is provided. In other embodiments, a method for treating the eye region (such as the malar bags, treating infraorbital laxity) is provided. In multiple embodiments, by performing treatment at different depths, improvement of upper eyelid laxity and improvement of periorbital lines and texture can be achieved. By performing treatment at different locations in a single procedure, optimal clinical effects (such as softening, tightening) can be obtained. In multiple embodiments, the treatment methods described herein are non-invasive cosmetic procedures. In some embodiments, the method can be used in combination with invasive procedures that are desired to achieve the effect of tightening the skin, such as surgical facelift or liposuction. In various embodiments, these methods can be applied to any part of the body.

[0089] In one embodiment, the transducer module 200 permits performance of a treatment sequence at or at a fixed depth beneath the skin surface. In one embodiment, the transducer module permits performance of a treatment sequence at one, two, or more variable or fixed depths beneath the dermis. In multiple embodiments, the transducer module includes a movement mechanism that is adapted and / or configured to direct ultrasound treatment at a fixed focus depth at a series of discrete thermal damage locations (hereinafter referred to as "thermal coagulation points" or "TCPs"). In one embodiment, the series of discrete TCPs has a treatment spacing within a range of from about 0.01 mm to about 25 mm (such as 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 5 mm, 10 mm, 20 mm, and any value range therebetween), and the jitter variation of the spacing is 1-50% (such as 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any range therebetween). For example, the spacing may be 1.1 mm or less, 1.5 mm or greater, from about 1.1 mm to about 1.5 mm, etc. In one embodiment, each TCP is discrete. In one embodiment, each TCP is overlapping. In one embodiment, the movement mechanism is adapted and / or configured to be programmed to provide a variable spacing between each TCP. In one embodiment, the jitter can be adapted and / or configured to provide a variable spacing between each TCP. In multiple embodiments, the transducer module includes a movement mechanism that is adapted and / or configured to direct ultrasound treatment sequentially 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, the second linear sequence being separated from the first linear sequence by a treatment distance. In one embodiment, the treatment distance between adjacent linear sequences of each TCP is within a range of from about 0.01 mm to about 25 mm. In one embodiment, the treatment distance between adjacent linear sequences of each TCP is within a range of from about 0.01 mm to about 50 mm. For example, the treatment distance may be 2 mm or less, 3 mm or greater, from about 2 mm to about 3 mm, etc. In multiple embodiments, the transducer module may include one or more movement mechanisms 400 that are adapted and / or configured to direct ultrasound treatment sequentially such that the TCPs are formed in a linear or substantially linear sequence of each thermal damage location separated by a treatment distance. In one embodiment, treatment is applied in a first direction 290 (such as a push). In one embodiment, treatment is applied in a direction opposite to the first direction 290 (such as a pull). In one embodiment, treatment is applied in the first direction 290 and in a direction opposite to the first direction (such as a push and a pull).In one embodiment, the treatment distances separating linear or substantially linear TCP sequences are the same or substantially the same. In one embodiment, for each adjacent pair of linear TCP sequences, the treatment distances separating the linear or substantially linear TCP sequences are different or substantially different.

[0090] 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 ultrasound imaging and ultrasound treatment. In one embodiment, the transducer module is only adapted and / or configured for treatment. In one embodiment, the imaging transducer can be attached to the handle of a probe or a wand. The first and second transducer modules are adapted and / or configured to be interchangeably coupled to the wand. The first transducer module is adapted and / or configured to apply ultrasound treatment to a first layer of tissue, while the second transducer module is adapted and / or configured to apply ultrasound treatment to a second layer of tissue. The second layer of tissue is at a different depth from the first layer of tissue.

[0091] In various embodiments, through controlled operation by the control system 300, the module 200 is implemented to deliver the transmitted energy 50 at an appropriate focal depth 278, distribution, timing, and energy level to achieve the desired treatment effect of controlled thermal damage, thereby treating at least one of the epidermal layer 502, dermal layer 503, adipose layer 505, SMAS layer 507, muscle layer 509, and / or subcutaneous layer 504. Figure 3 One embodiment of the depth corresponding to the depth of treating muscle is shown. In various embodiments, the depth can correspond to any tissue, tissue layer, skin, epidermis, dermis, subcutaneous layer, adipose, SMAS, muscle, blood vessel, nerve, or other tissue. During operation, the module 200 and / or the transducer 280 can also be scanned mechanically and / or electronically along the surface 501 to treat an extended area. Monitoring of the treatment area and surrounding structures can be provided before, during, and after delivering the ultrasound energy 50 to at least one of the epidermal layer 502, dermal layer 503, subcutaneous layer 504, adipose layer 505, SMAS layer 507, and / or muscle layer 509 to plan and evaluate the results and / or provide feedback to the controller 300 and the user through the graphical interface 310.

[0092] In one embodiment, the ultrasound system 20 generates ultrasound energy that is directed and focused beneath the surface 501. This controlled and focused ultrasound energy 50 creates thermocoagulation points or zones (TCPs) 550. In one embodiment, the ultrasound energy 50 creates voids in the subcutaneous tissue 510. In various embodiments, the emitted energy 50 is aimed at the tissue beneath the surface 501 to cut, ablate, coagulate, micro-ablate, manipulate, and / or cause TCPs 550 at a specified focal depth 278 in a tissue portion 10 beneath the surface 501. In one embodiment, during a treatment sequence, the transducer 280 moves in the direction shown by the arrow 290 at a specified interval 295 to create a series of treatment zones 254, each of which receives the emitted energy 50, thereby creating one or more TCPs 550. In one embodiment, the arrow labeled 291 shows an axis or direction orthogonal to the arrow 290, and the spacing of the TCPs 550 shows that the TCPs can be spaced orthogonally to the direction of movement of the transducer 280. In some embodiments, the orientation of the spaced TCPs can be set to any angle in the range of 0 - 180 degrees with respect to the arrow 290. In some embodiments, based on the orientation of the polarized regions on the transducer 280, the orientation of the spaced TCPs can be set to any angle in the range of 0 - 180 degrees.

[0093] In various embodiments, the transducer module may include one or more transducer elements. The transducer element may include a piezoelectrically active material, such as lead zirconate titanate (PZT), or may include 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 place of the piezoelectrically active material, the transducer module may include any other material adapted and / or configured to generate radiant and / or acoustic energy. In various embodiments, the transducer module is capable of being adapted and / or configured to operate at different frequencies and treatment depths. The transducer characteristics may be defined by an outer diameter (“OD”) and a focal length (FL). In one embodiment, the transducer is capable of being adapted and / or configured to have an OD of 19 mm and an FL of 15 mm. In other embodiments, other suitable OD and FL values may be used, such as an OD less than approximately 19 mm, greater than approximately 19 mm, etc., and an FL less than approximately 15 mm, greater than approximately 15 mm, etc. The transducer module is capable of being adapted and / or configured to apply ultrasonic energy at different target tissue depths. As described above, in a plurality of embodiments, the transducer module includes a movement mechanism adapted and / or configured to direct ultrasonic treatment in a linear or substantially linear sequence of respective TCPs, with a treatment spacing between respective TCPs. For example, the treatment spacing may be approximately 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, etc. In a plurality of embodiments, the transducer module may further include a movement mechanism adapted and / or configured to direct ultrasonic treatment in sequence such that the TCPs are formed in a linear or substantially linear sequence separated by the treatment spacing. For example, the transducer module is capable of being adapted and / or configured to form TCPs along a first linear sequence and a second linear sequence, the second linear sequence being spaced from the first linear sequence by a treatment spacing of approximately 2 mm to 3 mm. In one embodiment, the user may manually move the transducer module over the surface of the treatment area to produce adjacent linear sequences of TCPs. In one embodiment, the movement mechanism may automatically move the transducer module over the surface of the treatment area to produce adjacent linear sequences of TCPs.

[0094] Multi-Focus Region Sorting

[0095] In various embodiments, ultrasound imaging is used in conjunction with therapeutic tissue treatment. In various embodiments for improving ultrasound imaging, multiple focal zones are employed to obtain better signal quality and resolution over a depth range. For conventional diagnostic ultrasound scanners (linear, curved, phased array, etc.) that form two-dimensional ultrasound images without moving the transducer, the order in which these multiple focal zones are acquired is less important because the precise placement of these focal zones can be electronically controlled. Figure 3 Shown is focal zone imaging that does not move during imaging, which has an optional electronically steerable / translatable aperture. For non-moving imaging transducers, focal zone positioning is precise, and thus focal zone ordering is not employed. In traditional multi-focal zone imaging sequences, the order of focal zone interrogation does vary. In various embodiments, an "N" focal zone sequence includes 1, 2, 3, 4, 5, 6, 7, 8, 9, 10 or more focal zones. In one embodiment, for one focal zone, N = 1. In one embodiment, for four focal zones, N = 4. In one embodiment, for eight focal zones, N = 8. In the following embodiments, N = 4 is used, but any value of N can be used in various embodiments. For example, in the case of N = 4, the 4-focal zone sequence follows a traversal order (f1, f2, f3, f4) that is independent of the position and direction of movement.

[0096] However, for moving imaging transducers (such as mechanically translated or steered arrays), this can become problematic, especially at increased speeds, because there are position differences as the transducer sweeps across multiple focal zones. This positional misregistration is particularly magnified when forming bidirectional imaging (forming images from left to right and from right to left) because the interrogation regions between the two images may be different. This principle can be illustrated with the case of linear translation, but the present disclosure applies to all types of motion, including but not limited to translation, rotation, bending, two-dimensional and three-dimensional motion, or any combination thereof.

[0097] Embodiments of the imaging system disclosed herein address these misregistrations. In some cases, spatial misregistration occurs because the transducer moves at one or more speeds during imaging. In particular, between two images, extreme focal zones may be in separate positions, although they should interrogate the same region of interest. When forming a two-dimensional image using a mechanically translated / steered transducer, the transmit / receive position of the transducer changes because the transducer has also moved during the propagation time associated with the ultrasound signal.

[0098] In one embodiment, the first direction travel (outward (or outbound)) sequence should proceed in order (f1, f2, f3, f4), while the second direction travel (return) sequence is (f1, f2, f3, f4) or (f4, f3, f2, f1), thus allowing better registration of the two images. In one embodiment, the rightward travel (outward) sequence should proceed in order (f1, f2, f3, f4), while the leftward travel (return) sequence is also (f1, f2, f3, f4), thus allowing better registration of the two images( Figure 4 ). In one embodiment, an alternative sequence is proposed such that the rightward travel (outward) sequence should proceed in order (f1, f2, f3, f4), while the leftward travel (return) sequence proceeds in the reverse order (f4, f3, f2, f1), thus allowing better registration of the two images( Figure 5 ). In various embodiments, the directions can be left, right, forward, backward, up, down, clockwise or counterclockwise, and / or a combination of rotational and translational movements.

[0099] Figures 4 - 7 Embodiments of direction - related focus area sorting are shown. The leftward travel sequence can repeat or reverse the order relative to the rightward travel sequence. Thus, the focus area alignment is improved. In addition, the acquisition positions can be staggered so that the same region of interest is better registered between the two images. Figures 4 - 7 Embodiments of direction - related focus area sorting with different trigger positions are shown. By staggering the trigger positions, the spatial registration between the rightward travel and leftward travel A - lines is further improved. In one embodiment, the imaging system employs a novel sequence of two consecutive A - lines that continuously follows the travel order (line 1: f1, f2, f3, F4; line 2: f1, f2, f3, f4). In one embodiment, the imaging system employs a new sequence of two consecutive A - lines that continuously follows the travel order (line 1: f1, f2, f3, F4; line 2: f4, f3, f2, f1). This sequence can be repeated throughout the field of view, and assuming an even number of vectors in the field of view, the return sequence can have the exact same alternating - pattern focus area sequence, and the two images will be registered.

[0100] Figure 7Shows an embodiment of direction - related focus zone ordering with sequences (f1 - f2 - f3 - f4) and (f1 - f2 - f3 - f4) on consecutive A - lines or alternating between (f1 - f2 - f3 - f4) and (f4 - f3 - f2 - f1). In one embodiment, the entire field of view is traversed by an even number of A - lines, and the focus sequences traveling left and right are the same. The trigger positions between two images are still different. In various embodiments, multi - focus zone imaging facilitates better correlation between images formed for first - direction travel and second - direction travel. In various embodiments, multi - focus zone imaging facilitates improving the effectiveness of B - mode imaging at faster (e.g., 2 - fold, 3 - fold, 4 - fold) scan rates. In various embodiments, multi - focus zone imaging is applied to any number of focus zones greater than 1. In various embodiments, the number of focus zones is two, three, four, five, six, seven, eight, nine, ten or more.

[0101] According to various embodiments, for cosmetic treatment, an ultrasound treatment system generates one, two or more simultaneously treated treatment points and / or focus zones under the skin surface. The beam movement can be left - right, up - down and / or at an angle. In one embodiment of mechanical jitter, the movement of the motion mechanism is fast enough to create a flatter temperature distribution around the expected TCP, which allows reducing the total acoustic energy for the same affected tissue volume, or using the same total acoustic energy for a larger affected tissue volume, or achieving any combination thereof. According to various embodiments, frequency modulation modifies the position of the focus zone and / or the spacing between focus zones such that the electronic jitter of the beam through frequency modulation precisely changes and / or moves the position of the beam focus. For example, in one embodiment, a small frequency swing can be used to jitter a 1.5 - mm spacing by ±0.1 mm. In various embodiments, a frequency swing can be used to jitter one or more of 0.5, 0.75, 1.0, 1.2, 1.5, 2.0 - mm spacings by ±0.01, 0.05, 0.1, 0.12, 0.15, 0.20, 0.25, 0.30 mm. In various embodiments, the frequency is modulated by 1 - 200% (e.g., 1%, 5%, 10%, ....... 200% and any range therein).

[0102] According to various embodiments, a cosmetic ultrasound treatment system and / or method can non-invasively generate single or multiple jittering cosmetic treatment zones and / or thermocoagulation points, where the ultrasound is focused at one or more positions in a treatment region within tissue beneath the skin surface and is moved by a change in frequency (e.g., by frequency modulation). Some systems and methods provide cosmetic treatment at different places in the tissue, such as at different depths, heights, widths, and / or positions. In one embodiment, a method and system include 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, a surface region of interest, and / or a subcutaneous region of interest in a treatment region of interest. In one embodiment, a method and system include a transducer system configured to provide ultrasound treatment to more than one region of interest, such as between at least two points at different positions in a region of interest in the tissue (e.g., at fixed or variable depths, heights, widths, and / or orientations). For imaging of the cosmetic treatment zone and / or for regions of interest in the tissue, some embodiments can split the beam to focus at two, three, four, or more foci (e.g., multiple foci, multi-foci). The position and / or jitter of the foci can be arranged axially, transversely, or otherwise within the tissue. Some embodiments can be configured for spatial control, such as by positioning and / or jittering of the foci, changing the distance from the transducer to a reflective surface, and / or changing the angle of the energy focused or unfocused to the region of interest, and / or be configured for temporal control, such as by controlling changes in the frequency, drive amplitude, and timing of the transducer. In some embodiments, the positioning and / or jittering of multiple treatment zones or foci are achieved by polarization, phase polarization, biphasic polarization, and / or polyphase polarization. In some embodiments, the positioning of multiple treatment zones or foci is achieved by phase modulation, e.g., in one embodiment, by electrical phase modulation. As a result, it is possible to dynamically control over time the position of the treatment zone, the number, shape, size, and / or volume of the treatment zones or lesion positions in the region of interest, and changes in the thermal conditions.

[0103] According to various embodiments, a cosmetic ultrasound treatment system and / or method may use one or more of frequency modulation, phase modulation, polarization, non-linear acoustics, and / or Fourier transform to generate multiple cosmetic treatment zones to produce any spatial periodic pattern having one or more ultrasonic portions. In one embodiment, the system uses polarization at the ceramic level to provide single or multiple treatment zones simultaneously or sequentially. In one embodiment, the polarization pattern is a function of focus depth and frequency and uses an odd or even function. In one embodiment, the polarization pattern is applied based on focus depth and / or frequency and may be a combination of odd and even functions. In one embodiment, a process may be used in two or more dimensions to produce any spatial periodic pattern. In one embodiment, by using non-linear acoustics and Fourier transform, an ultrasonic beam is split axially and laterally to significantly reduce treatment time. In one embodiment, modulation of the system and amplitude modulation of the ceramic or transducer may be used to arrange multiple treatment zones in tissue sequentially or simultaneously.

[0104] In one embodiment, an aesthetic imaging and treatment system includes an ultrasound probe that includes an ultrasound transducer configured to apply ultrasound treatment to tissue at multiple locations at a focus depth using electronic jitter of a multi-energy beam aperture employing frequency modulation. In one embodiment, the system includes a control module coupled to the ultrasound probe for controlling the ultrasound transducer.

[0105] In one embodiment, the system includes jitter configured to provide variable spacing between multiple independent cosmetic treatment zones. In one embodiment, a series of independent cosmetic treatment zones has a treatment spacing in the range of from 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 value range therebetween), and the jitter of the spacing is changed by 1 - 50% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any range therebetween). In one embodiment, a series of independent cosmetic treatment zones has a treatment spacing in the range of from 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 value range therebetween), and the jitter of the spacing is changed by 1 - 50% (e.g., 1%, 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, and any range therebetween).

[0106] In one embodiment, the system further includes a mobile mechanism configured and programmed to provide a constant or variable spacing between a plurality of independent beauty treatment zones. In one embodiment, a series of independent beauty treatment zones have a treatment spacing in the range of from about 0.01 mm to about 25 mm (e.g., 0.1, 0.5, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 19 mm or any range or value therein). In one embodiment, a series of independent beauty treatment zones have a treatment spacing in the range of from 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, treatment zones are provided along a distance of about 25 mm. In one embodiment, treatment zones are provided along a distance of about 50 mm. In various embodiments, treatment zones are 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, treatment zones are provided along a straight and / or curved distance.

[0107] For example, in some non-limiting embodiments, the transducer can be configured for 0.5 mm, 1.0 mm, 1.5 mm, 2 mm, 3 mm, 4.5 mm, 6 mm, less than 3 mm, 0.5 mm to 5 mm, 1.5 mm to 4.5 mm, greater than 4.5 mm, greater than 6 mm, and any tissue depth in the range of 0.1 mm - 3 mm, 0.1 mm - 4.5 mm, 0.1 mm - 25 mm, 0.1 mm - 100 mm (e.g., 6 mm, 10 mm, 13 mm, 15 mm). In multiple embodiments, tissue is treated at a depth beneath the skin surface and the skin surface is not damaged. Instead, the treatment effect achieved at the depth beneath the skin surface results in a good appearance of the skin surface. In other embodiments, the skin surface is treated with ultrasound (e.g., at a depth less than 0.5 mm).

[0108] One benefit of the motion mechanism is that it enables more efficient, accurate, and precise use of the ultrasound transducer for imaging and / or treatment purposes. One advantage of this motion mechanism over a conventional fixed array of multiple transducers fixed in a space within a housing is that the fixed array is spaced at a fixed distance. In one embodiment, the transducer module is configured to provide an ultrasound treatment acoustic power in the range of about 1 W to about 100 W (e.g., 3 - 30 W, 7 - 30 W, 21 - 33 W) and a frequency in the range of about 1 MHz to about 10 MHz to heat tissue to cause coagulation. In one embodiment, the transducer module is configured to provide an ultrasound treatment acoustic power in the range of about 1 W to about 500 W peak or average energy (e.g., 3 - 30 W, 7 - 30 W, 21 - 33 W, 100 W, 220 W or higher) and a frequency in the range of about 1 MHz to about 10 MHz to heat tissue to cause coagulation. In some embodiments, transient energy is delivered. In some embodiments, average energy is delivered. In one embodiment, the acoustic power is in the range from 1 W to about 100 W and its frequency ranges from about 1 MHz to about 12 MHz (e.g., 1 MHz, 3 MHz, 4 MHz, 4.5 MHz, 7 MHz, 10 MHz, 2 - 12 MHz), or the acoustic power is in the range from about 10 W to about 50 W and its frequency ranges from about 3 MHz to about 8 MHz (e.g., 3 MHz, 4 MHz, 4.5 MHz, 7 MHz). In one embodiment, in the frequency range of about 1 MHz to about 12 MHz (e.g., 1 MHz, 4 MHz, 7 MHz, 10 MHz, 2 - 12 MHz), the acoustic power can be in the range of 1 W to about 500 W, or in the frequency range of about 3 MHz to about 8 MHz or 3 MHz to 10 MHz, the acoustic power can be in the range of about 10 W to about 220 W. In one embodiment, at a frequency of about 4.3 MHz, the acoustic power is about 40 W, and at a frequency of about 7.5 MHz, the acoustic power is about 30 W. The acoustic energy generated by this acoustic power can be about 0.01 joules ("J") to about 10 J or about 2 J to about 5 J. The acoustic energy generated by this acoustic power can be about 0.01 J to about 60000 J (e.g., for body shaping, submental fat, abdomen and / or flanks, arms, inner thighs, outer thighs, buttocks, abdominal laxity, cellulite through overall heating), about 10 J or about 2 J to about 5 J. In one embodiment, the acoustic energy is in the range less than about 3 J. In various embodiments, the treatment power is 1 kW / cm 2 to 100 kW / cm 2 、15 kW / cm 2 to 75 kW / cm 2 、1 kW / cm 2 to 5 kW / cm2 , 500 W / cm 2 to 10 kW / cm 2 , 3 kW / cm 2 to 10 kW / cm 2 , 15 kW / cm 2 to 50 kW / cm 2 , 20 kW / cm 2 to 40 kW / cm 2 and / or 15 kW / cm 2 to 35 kW / cm 2 .

[0109] In the various embodiments described herein, the procedure is entirely cosmetic and not a medical act. For example, in one embodiment, the methods described herein do not need to be performed by a doctor, but rather at a spa or other beauty establishment. In some embodiments, a system can be used for non-invasive cosmetic treatment of the skin.

[0110] In various embodiments, the ultrasound treatment is at least one of a facelift, brow lift, chin lift, eye treatment, wrinkle reduction, laxity improvement, buttock lift, scar reduction, burn treatment, skin tightening (such as abdominal laxity treatment), blood vessel reduction, sweat gland treatment, sunspot removal, fat treatment, and cellulite treatment.

[0111] In multiple embodiments, a system and method are provided for successfully improving ultrasound imaging of tissue while in motion (such as when an imaging transducer is on a motion mechanism). In various embodiments, higher resolution is achieved. In various embodiments, better imaging signal quality is obtained. In various embodiments, ultrasound imaging is used in conjunction with therapeutic tissue treatment.

[0112] In various embodiments, an ultrasound treatment and imaging system is provided that is configured to reduce imaging misalignment. The system includes an ultrasound probe that includes an ultrasound treatment transducer adapted to apply ultrasound treatment to tissue, an ultrasound imaging transducer adapted to image the tissue, and a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction. In one embodiment, the ultrasound imaging transducer is mechanically attached to the motion mechanism. In one embodiment, the first direction is linear. In one embodiment, the second direction is linear. In one embodiment, the first direction is parallel to the second direction. In one embodiment, the first direction is opposite to the second direction. In one embodiment, the ultrasound imaging transducer images in a first sequence of focus zones (such as f1, f2,..., f N ) as it travels in the first direction, and the ultrasound imaging transducer images in a second sequence of focus zones (such as f1, f2,..., fN ; or f N , ……, f2, f1) to image, and improve the spatial registration between the imaging in the first direction and the imaging in the second direction by staggering the trigger positions. In one embodiment, the control module is coupled to the ultrasound probe for controlling the ultrasound imaging transducer.

[0113] In various embodiments, there is provided an ultrasound therapy and imaging system configured to reduce imaging misregistration, the system including an ultrasound probe that includes an ultrasound therapy transducer adapted to apply ultrasound therapy to tissue, an ultrasound imaging transducer adapted to image the tissue, and a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction. In one embodiment, the ultrasound imaging transducer is mechanically attached to the motion mechanism, wherein the first direction is linear, wherein the second direction is linear, wherein the first direction is parallel to the second direction, wherein the first direction is opposite to the second direction, wherein the ultrasound imaging transducer images in a first sequence of focus zones (f1, f2, f3, f4) when traveling in the first direction, and wherein the ultrasound imaging transducer images in a second sequence of focus zones (f1, f2, f3, f4) or (f4, f3, f2, f1) when traveling in the second direction. In one embodiment, the spatial registration between the imaging in the first direction and the imaging in the second direction is improved by staggering the trigger positions, wherein the imaging system employs a sequence of two consecutive A-lines that continuously follow the travel order (line 1: f1, f2, f3, F4; line 2: f1, f2, f3, f4); and a control module coupled to the ultrasound probe to control the ultrasound imaging transducer. In one embodiment, the spatial registration between the imaging in the first direction and the imaging in the second direction is improved by staggering the trigger positions, wherein the imaging system employs a sequence of two consecutive A-lines that continuously follow the travel order (line 1: f1, f2, f3, F4; line 2: f4, f3, f2, f1); and a control module coupled to the ultrasound probe to control the ultrasound imaging transducer.

[0114] In various embodiments, there is provided an ultrasound therapy and imaging system configured to reduce imaging misregistration, the system including an ultrasound probe that includes an ultrasound therapy transducer adapted to apply ultrasound therapy to tissue, an ultrasound imaging transducer adapted to image the tissue, and a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction. In one embodiment, the ultrasound imaging transducer is mechanically attached to the motion mechanism. In one embodiment, the first direction is opposite to the second direction. In one embodiment, the ultrasound imaging transducer images in a sequence of focus zones (f1, …, f N ) where N>1. In one embodiment, the ultrasound imaging transducer images in a second sequence of focus zones (f1, ……, fN ) or (f N , ……, f1) imaging. In one embodiment, spatial registration between imaging in the first direction and imaging in the second direction is improved by staggering trigger positions. In one embodiment, the imaging system employs a direction-dependent focus zone ordering that repeats (f1 - …… - f N ) and (f1 - …… - f N ) and / or alternates between (f1 - …… - f N ) and (f N - …… - f1); and a control module coupled to the ultrasound probe to control the ultrasound imaging transducer.

[0115] In one embodiment, the first movement direction of the transducer is any one or more directions in the group consisting of a straight line, a rotation, and a curve. In one embodiment, the second direction is the reverse path of the first direction. In one embodiment, the first movement direction occurs in multiple dimensions and the second direction is the reverse path of the first direction. In one embodiment, the ultrasound imaging transducer is designated as (f1, ……, f N)sequential imaging of the first focus zone sequence, where N > 1 (for example, N is 2, 3, 4, 5, 6 or greater). In one embodiment, the ultrasound treatment transducer is configured to treat tissue at a first set of locations within a first aesthetic treatment area and at a second set of locations within a second aesthetic treatment area, the first area being different from the second area. In one embodiment, the ultrasound treatment transducer is adapted to apply ultrasound treatment using amplitude modulation, whereby multiple portions of the ultrasound transducer are adapted to emit ultrasound treatment at multiple acoustic intensity amplitudes, where the first amplitude is different from the second amplitude. In one embodiment, at least a portion of the ultrasound transducer is adapted to emit ultrasound treatment at two or more acoustic intensity amplitudes, and wherein the amplitude of the ultrasound treatment emitted by at least a portion of the piezoelectric body varies over time. In one embodiment, the ultrasound transducer comprises a piezoelectric material, and multiple portions of the ultrasound transducer are adapted to produce multiple corresponding piezoelectric material variations in response to an electric field applied to the ultrasound transducer. In one embodiment, the multiple piezoelectric material variations include at least one of expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, the ultrasound transducer is adapted to apply ultrasound treatment by phase shift, whereby multiple portions of the ultrasound transducer are adapted to emit ultrasound treatment at multiple acoustic intensity phases, where the first phase is different from the second phase. In one embodiment, the multiple phases include discrete phase values. In one embodiment, the ultrasound transducer is adapted to apply ultrasound treatment using amplitude modulation, whereby multiple portions of the ultrasound transducer are adapted to emit ultrasound treatment at multiple acoustic intensity amplitudes, where the first amplitude is different from the second amplitude; and to apply ultrasound treatment, whereby multiple portions of the ultrasound transducer are adapted to emit ultrasound treatment at multiple acoustic intensity phases, where the first phase is different from the second phase. In various embodiments, the ultrasound treatment is at least one of the following treatments: facelift, brow lift, chin lift, eye treatment, wrinkle reduction, sagging improvement, buttock lift, scar reduction, burn treatment, skin tightening (e.g., sagging treatment), blood vessel reduction, sweat gland treatment, sunspot removal, fat treatment, cellulite treatment, vaginal tightening, and acne treatment.

[0116] In various embodiments, a method for reducing imaging misregistration in a mobile ultrasound probe is provided, the method comprising staggering the trigger positions for spatial registration between imaging in a first direction and imaging in a second direction using the ultrasound probe, the ultrasound probe comprising an ultrasound treatment transducer adapted to apply ultrasound treatment to tissue, an ultrasound imaging transducer adapted to image the tissue, and a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction, wherein the ultrasound imaging transducer is mechanically attached to the motion mechanism, wherein the first direction is opposite to the second direction, and wherein the ultrasound imaging transducer images in a focus zone sequence order (f1,..., f N )where N > 1, and wherein when traveling in the first direction, the ultrasound imaging transducer images in a first focus zone sequence order (f1,..., fN ) Imaging, wherein when traveling in a second direction, the ultrasonic imaging transducer images in a second sequence of focus zones (f1, ……, f N ) or (f N , ……, f1).

[0117] In one embodiment, N = any value in the group consisting of 2, 3, 4, 5, 6, 7, 8, 9, and 10. In one embodiment, N = 2. In one embodiment, N = 4. In one embodiment, N = 6. In one embodiment, N = 4. In various embodiments, the ultrasonic treatment is at least one of facelift, eyebrow lift, chin lift, eye treatment, wrinkle reduction, laxity improvement, buttock lift, scar reduction, burn treatment, tattoo removal, skin tightening (such as abdominal laxity treatment), vein removal, vein reduction, sweat gland treatment, hyperhidrosis treatment, sunspot removal, fat treatment, vaginal tightening, and acne treatment.

[0118] Minimize Imaging Artifacts from Acoustic Reflections

[0119] In various embodiments, systems and methods for ultrasonic imaging of tissue are adapted to and / or configured to image using one or more focus zones in the tissue. In one embodiment, imaging is performed using a single focus zone. In one embodiment, imaging is performed using a single focus zone without treatment. In one embodiment, imaging is performed using a single focus zone and treatment is performed. In various embodiments, imaging is performed using two, three, four, or more focus zones. In various embodiments, imaging is performed using two, three, four, or more focus zones without treatment. In various embodiments, imaging is performed using two, three, four, or more focus zones and treatment is performed. In various embodiments, the ultrasonic transducer for imaging is arranged to be in direct contact with tissue such as the skin surface through acoustic coupling for imaging one or more focus zones under the skin surface. In various embodiments, the ultrasonic transducer for imaging has an offset gap between the imaging transducer and a housing portion in the ultrasonic probe (such as at an acoustic window, such as a PEEK window), whereby the housing portion is arranged to be in contact with tissue such as the skin surface through acoustic coupling for imaging one or more focus zones under the skin surface. In some embodiments, the ultrasonic transducer for imaging has an offset gap between the imaging transducer and a housing portion using two or more (such as 2, 3, 4, 5, 6, or more) focus zones, and this offset gap generates multipath artifacts from ultrasonic energy that bounces between the imaging transducer and (i) the acoustic window and / or (ii) the region being imaged. These artifacts may blur the clarity of the imaging.

[0120] Please refer to Figure 8A and8B , in some embodiments, when ultrasonic energy passes through an acoustic medium (such as an acoustic couplant, fluid, gel, liquid, such as water, glycerol, saline, and any combination thereof) within the housing of an ultrasonic imaging system, multipath artifacts 810 may be generated. In some embodiments, the artifacts are generated in the acoustic medium within the offset gap 800 between the imaging transducer (such as an imaging array) and the target tissue. In some embodiments, the offset gap is 10.9, 11.1, 12.4, or 13.8 mm, but it may also vary according to transducer temperature, the amount of fluid within the transducer, and the pressure applied to the acoustic window (atmospheric pressure or pressure applied by the patient or clinician). The multipath artifact 810 can be an ultrasonic artifact where the ultrasonic beam is reflected at an angle such that only a portion of the ultrasonic beam returns to the transducer. Such an artifact may be generated by a portion of the acoustic energy that is trapped and bounced within the transducer housing between the imaging array and the acoustic window. More specifically, the multipath artifact 810 may be generated by acoustic energy that is reflected and repeatedly bounced between the imaging array and the acoustic window. In one embodiment, these reflections may result in the appearance of the multipath artifact 810 at integer multiples of the distance between the imaging array and the acoustic window. The multipath artifact 810 obscures and / or masks the clarity of the image generated by the ultrasonic imaging system and may lead to an invalid or inefficient interpretation of the resulting image.

[0121] In one embodiment, when performing B-mode imaging at a high pulse repetition frequency (“PRF”), such as when acquiring multiple focal zones at certain depths (such as 0.1, 0.2, 0.3, 0.4, 0.5, 0.6, 0.7, 0.8, 0.9, 1.0, 1.1, 1.2, 1.3, 1.4, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 8, 9, 10, 11, 12 mm and any ranges and values therein), artifacts may be observed in consecutive imaging lines. This may result in a blurred or unclear image, or an image that may lead to an invalid or inefficient interpretation of the resulting image. In one embodiment, the multipath artifact 810 from the imaging emission of a given A-line / focal zone may appear in the image data of subsequent A-lines / focal zones. Thus, the image generated from the partially reflected ultrasonic beam may also generate the multipath artifact 810 throughout the image, rather than just generating the multipath artifact 810 in one focal zone. Figure 8A This embodiment is schematically illustrated in Figure 8A As shown, due to the ultrasonic energy repeatedly bouncing across the offset gap 800 between the imaging array and the acoustic window and repeatedly bouncing between the imaging array and the bottom of the image of the regional distance 801, the multipath artifact 810 may occur from the transmission (Tx1) of the focal zone 1. This is represented as Figure 8A the dashed line 802 of Tx1 shown in Figure 8AAs shown, over time, multipath artifact 810 continues to form from the rebounding and reflection of overlapping ultrasonic waves. When subsequently sorting the subsequent focus zone (Tx2) shown by the dashed line 804, the reverberations of multipath artifact 810 also appear in the imaging data. Figure 8A The presence of this Tx1 dashed line 802 during the imaging of the Tx2 dashed line 804 is shown by the crossing or overlapping Tx1 dashed line 802 and Tx2 dashed line 804. As Figure 8B shown, multipath artifact 810 is present in the focus zone 2 (Tx2) image 806 and makes the image partially blurred / unclear. In some embodiments, multipath artifact 810 may limit the imaging rate of the system because the waiting time (or delay) may have to be set to a long enough period of time so that the multipath artifact echoes are sufficiently attenuated. In various embodiments, the range of this period of time can be 30 to 60 microseconds (μs) (e.g., 30-35, 30-40, 30-45, 30-50, 30-55, 35-40, 40-45, 45-50, 50-55, 55-60, 35-55, 35-50, 35-45, 40-50, 40-55, 40-60, 45-55, 45-60, 50-60, 55-60 μs, and values and ranges therein).

[0122] Please refer to Figure 9A and 9B , for maintaining a static or constant offset gap distance 900 between the imager and the acoustic window, the waiting time or pulse repetition interval (PRI) can be strategically selected or calculated to reduce or eliminate multipath artifacts. For example, the waiting time interval can be strategically selected such that the multipath artifacts (in the offset gap 900 between the imaging array and the acoustic window, and between the imaging array and the bottom distance 901 of the imaging area) that appear in the subsequent focus zone image data are outside the field of view of the transducer. As Figure 9A shown, the Tx1 dashed line 902 does not intersect the Tx2 dashed line 904, but is parallel. In this embodiment, the multipath artifact 910 (not shown) is outside the field of view of the imaging. In addition, as Figure 9B shown, the multipath artifact 910 (not shown) echoes are not in the generated Tx2 image 906, but outside the image acquisition time of Tx2 904. In various embodiments, the static waiting time can be in the range of 30-60 microseconds (e.g., 30, 32, 32.5, 34, 36, 36.5, 37, 37.5, 38, 39, 39.5, 40, 42, 44, 44.5, 45, 45.5, 46, 48, 50, 52, 54, 56, 58, 60 and values and ranges therein).

[0123] In some embodiments, the offset gap 1000 between the imaging transducer and the acoustic window varies (e.g., changes, is dynamic) between 1000 - 1000'. The dynamic offset gaps 1000, 1000' can change with changes in the temperature, pressure, and / or volume of the coupling medium. The temperature, pressure, and / or volume of the coupling medium may change and fluctuate, thus deflecting the acoustic window and changing the offset gap distances 1000 - 1000'. In one embodiment, over time as the system is used, the ultrasound system housing may lose coupling medium through evaporation and / or leakage. In one embodiment, the temperature of the ultrasound system housing of the coupling medium changes over time. In one embodiment, the pressure of the ultrasound system housing of the coupling medium changes over time. In one embodiment, when a user or an object presses on the acoustic window, the offset gaps 1000, 1000' of the acoustic window can be changed, thus deflecting the acoustic window and changing the offset gaps 1000, 1000'. As Figure 10A shown in the embodiment of

[0124] The calculations for determining the timing to reduce imaging artifacts for dynamic offset are more complex than for static offset. For static offset, the timing calculations remain the same. However, for dynamic offset, the timing calculations change. Using static calculations in a dynamic imaging environment may result in the appearance of imaging artifacts.

[0125] Figure 11 A flowchart is shown for dynamically setting the ultrasound imaging transmit wait time / pulse repetition interval (PRI) to reduce imaging multipath artifacts 810, 910, 1010 according to one embodiment. In one embodiment, the dynamic wait time calculation is achieved by expanding the imaging region to include the depths where the acoustic window may be located. Using these additional depths, the dynamic offset distances 1000, 1000' are measured within the B-mode image. This distance is measured by determining the offset depth of the first echo of the acoustic window. The speed of sound of the transducer coupling fluid at a given temperature is determined. The offset depth is calculated by converting the round-trip time. The timing of subsequent multipath artifacts is calculated by taking an integer multiple of the round-trip time. In some embodiments, the speed of sound can be a constant value, or, if the internal coupling fluid temperature is also monitored, then the speed of sound can be determined as a function of temperature. In some embodiments, the system can then dynamically set the wait time or pulse repetition interval to perform subsequent imaging transmit sequences, where the multipath artifact 1010 appears at a time outside the receive echo sampling interval of subsequent transmissions. In some embodiments, this calculation can be performed for each image frame, A-line, or transmit for a focused region. Additionally, in some embodiments, the focused regions can also be set at any interval.

[0126] Please refer further to Figure 11 which shows a method 1102 for dynamically setting a waiting time or a pulse repetition interval. At block 1104, the system determines the depth of the first acoustic window echo. This allows the transducer to be customized for the ultrasound image generated by the actual acoustic window being scanned. At block 1106, the system converts the determined depth into time. This conversion is based on the time of flight and the speed of sound in the acoustic medium. In one embodiment, at block 1108, the calculated time is multiplied by an integer to determine the number of times multipath artifacts may occur. At block 1110, a waiting time or a pulse repetition interval is selected. Then, the selected waiting time or pulse repetition interval can position the multipath artifacts outside of subsequent image acquisitions. This dynamically sets the transmit waiting time or the pulse repetition interval and eliminates multipath echo artifacts.

[0127] Please refer to Figure 12A and Figure 12B In some embodiments, a pulse repetition interval (PRI, expressed in units of time, such as 30 - 60 microseconds, such as 30, 32, 32.5, 34, 36, 36.5, 37, 37.5, 38, 39, 39.5, 40, 42, 44, 44.5, 45, 45.5, 46, 48, 50, 52, 54, 56, 58, 60, and values and ranges therein) is selected for an imaging sequence that utilizes multi-focus zone imaging. In one embodiment, a static PRI is implemented. In one embodiment, a dynamic PRI is implemented. In one embodiment, multipath echo artifacts 1210 are generated at a specific region within the receive echo sampling interval of the imaging sequence. In one embodiment, multi-focus zone images are blended into a single image, whereby image regions containing the artifacts 1210 are not selected for display. This can be implemented when there is sufficient time between lateral positions to eliminate multiple echo artifacts 1210. This calculation can be performed for each image frame, each A-line, or each focus zone transmit. As Figure 12A shown, the image formed from the first focus zone transmit Fz1 does not contain the artifact 1210, but for example, subsequent focus zone images Fz2 contain the artifact 1210. However, as Figure 12B shown, when the focus zone images are blended to form a single image, the first focus zone image Fz1 is used at the depths where the artifact 1210 is present in other focus zone images Fz2, Fz3, Fz4.

[0128] In various embodiments, 2, 3, 4, 5, 6, 7, 8 or more focus zones are employed. In some embodiments, as Figure 12A and Figure 12BAs shown, four focusing zones Fz1, Fz2, Fz3, and Fz4 are employed. In one embodiment, the imaging sequence employs a sufficient waiting time between the focusing zone 4 at one lateral position and the focusing zone 1 at a subsequent lateral position. As a result, multipath echo artifacts appear only in the focusing zones 2 through 4 (Fz2, Fz3, Fz4). In Figure 12A and 12B the regions of all four focusing zone images demarcated by the black dashed lines are blended and combined to form a single combined image. In one embodiment, as Figure 12B shown, the blending zone is set dynamically such that no multipath artifacts appear in the final image. As Figure 12B shown, by varying the sizes of the four squares, the multipath artifacts are effectively cropped out of the final image.

[0129] In one embodiment, calculating the depth at which multipath artifacts are present in an image includes the following steps:

[0130] Let d0 be the depth of the first echo of the acoustic window detected in the B-mode image. Assuming a constant speed of sound propagation, the time (t0) between the initial imaging transmission and the arrival of this echo is defined as:

[0131]

[0132] where c f (T) is the speed of sound in the internal transducer fluid. This speed of sound value can be constant or a function of temperature (T).

[0133] Thus, the time (t N ) at which the multipath echo artifacts reach the imaging array will occur at integer multiples of t0:

[0134] t N = (N + 1)·t0, N = 1, 2, 3,...

[0135] If the axial field of view of the displayed image is defined at all depths d, where:

[0136] d min ≤ d ≤ d max

[0137] and d min and d max are the minimum depth and maximum depth of the displayed image, respectively, then the dynamic time delay t del (N) between successive imaging transmissions can be selected such that the times of two successive multipath echoes (t N and t N+1 ) lie outside the axial field of view, such that:

[0138]

[0139] where c is defined as the speed of sound in the target medium / within the patient.

[0140] Designate t del (N) as:

[0141]

[0142] such that the multipath echo is at a relative depth k within the image. When k = 0, the artifact is at the top of the image; when k = 1, the artifact is at the bottom of the image.

[0143] Regardless of whether t del ( N ) is static or dynamic, given its value, the above equation can be rearranged to solve for k:

[0144]

[0145] After calculating the relative depth k at which the multipath artifact appears in the image, the focus zone blend depth can be dynamically selected to exclude the artifact from the finally displayed image. For example, in one embodiment, the transducer fluid is water, at room temperature, c f = 1480 m / s, and when imaging into soft tissue, c = 1540 m / s. If the first echo from the acoustic window appears at 15 μs, then the fourth echo will appear at 60 μs. With a static PRI of 36.5 μs, the minimum and maximum imaging depths (from the imaging transducer) are 10.9 mm and 20.9 mm, then the relative depth (k) will be 0.68. Thus, the focus zone blend point can be selected such that the first focus zone encompasses this relative depth and thus the artifact will not be included in the finally displayed image.

[0146] Improve Imaging Alignment

[0147] In various embodiments, the imaging transducer may move across the field of view within the housing with the motion mechanism 400 at various speeds. In one embodiment, the motion mechanism 400 includes an axis, rod, screw, lead screw 401 for precise and repeatable motion of the imaging transducer along a straight line. For example, the imaging transducer moves into and out of the field of view along the axis, rod, screw, lead screw 401, i.e., in an in-ward and out-ward direction. In various embodiments, the speed at which the imaging transducer moves across the field of view may be 0.1 - 10.0 cycles (or Hertz, Hz) per second (e.g., 0.1, 0.5, 1.0, 1.5, 2.0, 2.5, 3.0, 3.5, 4.0, 4.5, 5.0, 5.5, 6.0, 6.5, 7.0, 7.5, 8.0, 8.5, 9.0, 9.5, and 10.0 cycles per second, including any values and ranges therein, such as 0.1 - 1.0, 0.1 - 2.0, 0.1 - 3.0, 0.1 - 4.0, 0.1 - 5.0, 1.0 - 2.0, 1.0 - 3.0, 1.0 - 4.0, 1.0 - 5.0, 2.0 - 3.0, 2.0 - 4.0, 2.0 - 5.0 cycles per second). In one embodiment, the imaging transducer moves across the field of view at a certain number of cycles per second. In one embodiment, B-mode images are acquired during the out-ward and in-ward motions of the imaging transducer. Thus, the frame rate may be increased or doubled to twice the number of cycles or frames per second. For example, in one embodiment, the imaging transducer moves across the field of view at a speed of 3.0 cycles per second. In one embodiment, B-mode images are acquired during the out-ward and in-ward motions of the imaging transducer, and the frame rate is increased or doubled to 6.0 cycles or frames per second. However, in some embodiments, there may be a slight misalignment of the spatial interrogation between the in-ward frame and the out-ward frame, resulting in an inaccurate image that appears to jitter. The misalignment may occur in multiple dimensions (e.g., up-down, left-right, in-out, x-axis, y-axis, z-axis). In addition, in some embodiments, the misalignment may include a rotational component. In various embodiments, such imaging misalignment may occur in the lateral (e.g., left-right) and / or vertical (e.g., in-out) dimensions. In some embodiments, the result of such imaging misalignment may be that the image may appear to jitter or may appear distorted, even if the imaging area is fixed or stationary.

[0148] Please refer to Figure 13 , in some embodiments, the lateral imaging misalignment is reduced and / or eliminated by implementing an image trigger offset. In some embodiments, the vertical misalignment is addressed by implementing at least one adaptive motion filter.

[0149] In some embodiments, lateral imaging misregistration is reduced or eliminated using outgoing and incoming frames by first acquiring imaging frames for outgoing and incoming actions having minimal or zero offset between the two directions. In one embodiment, the image trigger positions of the two frames can be the same. Subsequently, in some embodiments, a lateral cross-correlation can be performed on all incoming vectors. In one embodiment, the outgoing frame can be used as a reference to determine which lateral position within the outgoing frame best matches each incoming vector. Additionally, spatial interpolation can be utilized to match the vectors to sub-pixel accuracy to better resolve any misregistration within the frame.

[0150] In some embodiments, the outgoing image frame is used as a reference image. In one embodiment, the imaging transducer moves with a treatment transducer that delivers treatment in the outgoing direction. In one embodiment, a guidance marker within the displayed image indicates the location of the treatment dose.

[0151] In one embodiment, the lateral misregistration between the incoming vectors and the reference outgoing image can be reversed and subsequently edited to form a spatial image trigger offset curve for the next incoming frame acquisition. In one embodiment, the image trigger offset curve is physically unachievable. This can occur when the image trigger offset results in a time difference between successive lateral position image acquisitions that is shorter than the minimum necessary imaging time at a single position, causing an imaging acquisition data stream overflow and an error message indicating a display imaging trigger failure. To address this issue, in one embodiment, a cost function is constructed to minimize the difference between the ideal acquisition delay and the achievable acquisition delay.

[0152] In some embodiments, the cost function is performed by: seeding an absolute offset at each incoming location and combining the physical limits of the movement trajectory of the application module with the achievable trigger offsets that can be propagated along the entire lateral travel range of the module away from the absolute position. This results in N achievable trigger offset curves, where N is the total number of lateral positions within the image. A new set of imaging frames is acquired using the optimized, achievable incoming image trigger offset curves. The outgoing frames remain unchanged; however, an achievable imaging trigger delay can be applied to the incoming imaging frames acquisition. Next, in some embodiments, the process can be repeated to calculate a new set of misregistration offsets and a further refined incoming image trigger delay curve. The process can be repeated until the two images converge and any lateral misregistration is suppressed below a specified predetermined threshold. In some embodiments, when the misregistration is below the threshold, the imaging trigger offset can be programmed into the transducer such that all subsequent incoming images are acquired with these offsets applied. In one embodiment, redundant achievable trigger offset curves are eliminated. In the case where one curve intersects another curve, the two curves are blended and matched, and the cost function is used to remove suboptimal curves until a single optimized achievable trigger offset curve is obtained.

[0153] As Figure 13 shown, in one embodiment of method 1302, imaging inaccuracies, jitter, and / or blurring within the image due to misalignment between the incoming frames and the outgoing frames collected by the system are addressed, thereby improving lateral registration. At block 1304, the system applies a minimum or zero offset to the imaging frames. At block 1306, the system acquires the outgoing and incoming imaging frames secondarily. At block 1308, the system calculates the lateral misregistration. At block 1310, the system determines whether the misregistration is below a predetermined threshold. At block 1312, if the misregistration is below the predetermined threshold, then at least one image trigger offset is applied to all incoming image frames. However, at block 1314, if the misregistration is not below the predetermined threshold, then the system calculates an optimized incoming image trigger offset. If the misregistration is not below the predetermined threshold, then at block 1316, the system applies at least one image trigger offset to the incoming frames.

[0154] In some embodiments, after image acquisition, a temporal filter that mitigates vertical misregistration artifacts is utilized to address vertical imaging misregistration. In one embodiment, one or more temporal filters are applied to the B-mode image to eliminate or minimize vertical misregistration. The temporal filter can be applied by displaying the average of the previous N images, where N > 1 (e.g., N = 2, 3, 4, 5, 6, 7, 8, 9, 10, 25, 50, 100). This can be effective when imaging a static target and there is good spatial registration between the frames being averaged. However, in some embodiments, when the transducer or the target is moving, the temporal filter may introduce a blurring effect because the imaging frames without lateral registration are averaged together. In some embodiments, when the transducer is moving, an adaptive temporal motion filter averages and / or stabilizes the B-mode image. In some embodiments, motion detection can be performed with one or more sensors. Such sensors can include a gyroscope or an accelerometer. Additionally, in some embodiments, motion can be detected through the image itself. In one embodiment, the image correlation coefficient across multiple frames is calculated in real time.

[0155] In one embodiment, the temporal filter is activated (to achieve a blending effect) when optimizing the imaging correlation coefficient, and deactivated (to stop the blending effect) when the coefficient drops below a certain level.

[0156] In some embodiments, slight misalignment between consecutive frames (e.g., between the first and second images, between outgoing and incoming images) causes the correlation coefficient to vary according to the amount of misalignment. In one embodiment, at least two independent correlation coefficients are calculated to address this issue. In one embodiment, one coefficient is calculated using only the outgoing images, while a second coefficient is calculated using only the incoming images. This results in a more stable and reproducible coefficient between the imaging transducers, and the combination of at least two coefficients can maintain a calculation rate of at least 6 frames per second, for example. In one embodiment, a temporal stability filter is used based on calculating the correlation coefficient between the current frame and the imaging frames and comparing the correlation coefficient with a threshold. In one embodiment, the correlation coefficient is calculated using the current frame and the previous imaging frames (e.g., 2, 4, 6...) and compared with the threshold to determine whether to use the temporal stability filter.

[0157] Please refer to Figure 14 , inaccurate imaging transducer positioning between the inward and outward trajectories in a mobile imaging device may result in image jitter and / or blurring. In some embodiments, the temporal motion artifacts can be quantified. The correlation coefficient ("CC") between any two frames (e.g., frames F and G) is calculated using the raw in-phase quadrature (IQ) data.

[0158] F(t) = I1(t) * cos(ω * t) + Q1(t) * sin(ω * t)

[0159] G(t) = I2(t) * cos(ω * t) + Q2(t) * sin(ω * t)

[0160]

[0161] CC(t) = 1; when there is perfect correlation (F(t) = G(t))

[0162] CC(t) = 0; when there is no correlation

[0163] CC(t) = -1; when there is perfect anti - correlation

[0164] In some embodiments, these calculations provide the performance of two - dimensional pattern matching to maximize the correlation coefficient and determine the position of each pixel in the image.

[0165] In one embodiment, as Figure 15A shown, map the time - motion artifacts such that the time - motion of the artifacts appears mainly in the transverse direction. In one embodiment, as Figure 15B shown, map the time - motion artifacts such that the time - motion of the artifacts appears time - stable. In one embodiment, as Figure 15C shown, map the time - motion artifacts such that the time - motion of the artifacts appears consistent in depth. In some embodiments, the quantification of time - motion artifacts varies with the transducer.

[0166] Please refer to Figure 16A and Figure 16B , in one embodiment for solving imaging misregistration with only lateral shift, during the manufacture of each imaging transducer, measure a specific shift in that imaging transducer. Using the measured shift value, the imaging system shifts the imaging data to the nearest pixel (e.g., nearest - neighbor interpolation) based on the specific measured shift value. This method stabilizes the image only by lateral shift; however, it may not solve out - of - plane motion and sub - pixel decorrelation, which may cause the imaging shift to persist. Figure 16A An image showing the lateral shift of pixels during forward - backward and left - right movement is shown. Figure 16B An image showing stable pixel alignment after applying filtering is shown.

[0167] Please refer to Figure 17A and Figure 17B, in an embodiment for solving vertical imaging misregistration, temporal averaging is performed on consecutive imaging frames to solve the lateral misregistration problem. In some embodiments, temporal averaging of consecutive frames stabilizes the image. In some embodiments, temporal averaging of consecutive frames reduces the speckle contrast and the image resolution. Figure 17A Shows an image with pixels shifted in the vertical direction. Figure 17B Shows the stable pixel alignment obtained after applying filtering.

[0168] Please refer to Figure 18A and Figure 18B , in one embodiment, imaging misregistration and / or misalignment is reduced by shifting the data (such as the embodiments of Figure 16A and 16B ) and temporal averaging of consecutive frames (such as the embodiments of Figure 17A and 17B ). Shifting the data preserves the imaging resolution and corrects persistent large lateral motion artifacts (e.g., > 1 pixel). Temporal averaging of consecutive frames minimizes smaller motion artifacts in any direction (e.g., < 1 pixel).

[0169] In one embodiment, the correlation coefficient increases when the image is stationary. In one embodiment, the correlation coefficient is less than 0.5. In one embodiment, the correlation coefficient may vary with different imaging transducers. In one embodiment, the correlation coefficient contrast changes slightly when comparing shifted images. In one embodiment, there is sub - pixel and out - of - plane decorrelation.

[0170] As Figure 19 shown, in one embodiment, graph 1902 and graph 1904 show imaging pixels moving laterally over time. In one embodiment, graph 1906 shows the variation of the correlation coefficient over time.

[0171] Please refer to Figure 20 , in some embodiments, alternate - frame correlation better reflects and accounts for the presence of motion during imaging. In one embodiment, this helps to minimize the loss of frame rate and / or update rate.

[0172] In some embodiments, please refer to Figure 21 , the imaging system includes independently correlating outgoing and incoming images. In one embodiment, when the image is stationary, the correlation coefficient is close to 1, and when the image is moving, the correlation coefficient is close to 0. In one embodiment, the correlation coefficient varies between 0 - 1, 0 - 0.5, 0 - 0.4, 0 - 0.3, 0 - 0.2, or 0 - 0.1. In various embodiments, the correlation coefficient varies with the imaging transducer. Graph 2106 shows an embodiment where the correlation coefficient approaches 1 over time.

[0173] In some embodiments, refer to Figure 22A and Figure 22B , an adaptive temporal motion filter with lateral misregistration correction functionality corrects lateral misregistration when motion is sensed. In one embodiment, when the field of view is stationary, the temporal motion filter stabilizes the imaging. In one embodiment, when the field of view is moving, the temporal motion filter is disabled so as to maintain the temporal resolution.

[0174] Some of the embodiments and examples described herein are merely illustrative and are not intended to limit the full scope of the compositions and methods of the present invention. Within this scope, equivalent changes, modifications, and variations can be made to some of the embodiments, materials, compositions, and methods to obtain substantially similar results.

[0175] Some specific embodiments of the embodiments of the present invention are shown in the drawings and described in detail herein, and various modifications and substitutions can be made to these embodiments. However, it should be understood that these embodiments are not limited to the specific forms or methods disclosed. On the contrary, these embodiments should cover all modifications, equivalent forms, and alternative forms that fall within the spirit and scope of the various embodiments described and the appended claims. Any method disclosed herein does not necessarily have to be performed in the order described. The methods disclosed herein include certain actions taken by a practitioner; however, they may also include any explicit or implicit indication by any third party of these operations. For example, an action such as "couple the transducer module to the ultrasound probe" includes "instruct to couple the transducer module to the ultrasound probe". The scopes disclosed herein also cover any and all overlaps, sub-scopes, and combinations thereof. Terms such as "at most", "at least", "greater than", "less than", "between" include the recited numbers. Numbers preceded by terms such as "about" or "approximately" include the recited numbers. For example, "about 1 mm" includes "1 mm".

Claims

1. An ultrasonic imaging system configured to reduce imaging artifacts, the ultrasonic imaging system comprising: An ultrasonic probe, the ultrasonic probe comprising: An ultrasonic imaging transducer adapted to image a tissue region, A housing including an acoustic window, A dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies over time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance, An acoustic coupling medium located within the housing and configured to acoustically couple the ultrasonic imaging transducer to the acoustic window, A motion mechanism for moving the ultrasonic imaging transducer in a first direction and a second direction, Wherein, when traveling in the first direction, the ultrasonic imaging transducer images in a sequence of focus zones (f1, …, f N ), where N > 2, Wherein, when traveling in the second direction, the ultrasonic imaging transducer images in a second sequence of focus zones (f1, ……, f N ); and A control module coupled to the ultrasonic probe to control the ultrasonic imaging transducer, Wherein the control module is configured to reduce at least one multipath echo artifact by a dynamically set pulse repetition interval.

2. The ultrasonic imaging system according to claim 1, wherein the dynamically set pulse repetition interval is further configured to: Measure a first offset depth; Calculate a first offset time based on the first offset depth; Multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and Select a pulse repetition interval configured to place the at least one multipath echo artifact outside the displayed ultrasonic image.

3. An ultrasonic imaging system configured to reduce imaging artifacts, the ultrasonic imaging system comprising: An ultrasonic probe, the ultrasonic probe comprising: An ultrasonic imaging transducer adapted to image a tissue region, A housing including an acoustic window, A dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies over time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance, An acoustic coupling medium within the housing and configured to acoustically couple the ultrasonic imaging transducer to the acoustic window, A motion mechanism for moving the ultrasonic imaging transducer in a first direction and in a second direction, Wherein, when traveling in the first direction, the ultrasonic imaging transducer images in a sequence of focus zones (f1, …, f N ), where N > 2, Wherein, when traveling in the second direction, the ultrasonic imaging transducer images in a second sequence of focus zones (f1, ……, f N ); and A control module coupled to the ultrasonic probe to control the ultrasonic imaging transducer, Wherein the control module is configured to reduce at least one multipath echo artifact by one or more dynamically set focus zone mixing points.

4. The ultrasonic imaging system according to claim 3, wherein the at least one dynamically set focus zone mixing point is further configured to: Measure a first offset depth; Calculate a first offset time based on the first offset depth; Multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and Select at least one focus zone mixing point configured to place the at least one multipath echo artifact outside the displayed ultrasonic image.

5. The ultrasonic imaging system according to any one of claims 1-4, wherein the dynamic offset distance varies based on a change in volume of the acoustic coupling medium, and wherein the change in volume of the acoustic coupling medium is a result of evaporation or leakage of the acoustic coupling medium from the housing.

6. The ultrasonic imaging system according to any one of claims 1-4, wherein the dynamic offset distance varies based on a change in the temperature of the acoustic coupling medium.

7. The ultrasonic imaging system according to any one of the preceding claims, wherein the dynamic offset distance varies based on a change in the pressure of the acoustic coupling medium.

8. The ultrasonic imaging system according to any one of claims 1-4, wherein the dynamic offset distance varies with the speed of the moving mechanism in at least one of the first direction and the second direction.

9. The ultrasonic imaging system according to any one of claims 1-4, further comprising a treatment transducer configured to apply ultrasonic treatment to the tissue.

10. The ultrasonic imaging system according to any one of claims 1-4, wherein N is any one value of 2, 3, or 4.

11. An ultrasonic imaging system configured to reduce imaging artifacts, the ultrasonic imaging system comprising: An ultrasonic probe, the ultrasonic probe comprising: An ultrasonic imaging transducer adapted to image a tissue region, A housing including an acoustic window, A dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies with time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance, Means for moving the ultrasonic imaging transducer in a first direction and in a second direction, and A control module coupled to the ultrasonic probe to control the ultrasonic imaging transducer, wherein the control module is configured to reduce at least one multipath echo artifact by a dynamically set pulse repetition interval.

12. An ultrasonic imaging module configured to reduce imaging artifacts, the ultrasonic imaging module comprising: An ultrasonic imaging transducer adapted to image a tissue region, A housing including an acoustic window, A dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies with time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance, Means for moving the ultrasonic imaging transducer in a first direction and in a second direction, and A control module coupled to the ultrasonic probe to control the ultrasonic imaging transducer, wherein the control module is configured to reduce at least one multipath echo artifact by a dynamically set pulse repetition interval.

13. The ultrasonic imaging module according to claim 12, wherein the at least one dynamically set focus zone mixing point is further configured to: Measure a first offset depth; Calculate a first offset time based on the first offset depth; Multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and Select at least one focus zone mixing point configured to place the at least one multipath echo artifact outside the displayed ultrasonic image.

14. An ultrasonic imaging device configured to reduce imaging artifacts, comprising: An ultrasonic module, the ultrasonic module comprising: An ultrasonic imaging transducer adapted to image a tissue region, A housing, including an acoustic window, A dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies over time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance, A device for moving the ultrasonic imaging transducer in a first direction and in a second direction, and A control module, coupled to the ultrasonic probe to control the ultrasonic imaging transducer, wherein the control module is configured to reduce at least one multipath echo artifact by a dynamically set pulse repetition interval.

15. The ultrasonic imaging device according to claim 14, wherein at least one dynamically set focus zone mixing point is further configured to: Measure a first offset depth; Calculate a first offset time based on the first offset depth; Multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and Select at least one focus zone mixing point configured to place the at least one multipath echo artifact outside the generated ultrasonic image.

16. The ultrasonic imaging device according to any one of claims 14-15, wherein the dynamic offset distance varies based on a change in the volume of the acoustic coupling medium, and wherein the change in the volume of the acoustic coupling medium is a result of evaporation or leakage of the acoustic coupling medium from the housing.

17. The ultrasonic imaging device according to any one of claims 14-15, wherein the dynamic offset distance varies based on a change in the temperature of the acoustic coupling medium.

18. The ultrasonic imaging device according to any one of claims 14-15, wherein the dynamic offset distance varies based on a change in the pressure of the acoustic coupling medium.

19. The ultrasonic imaging device according to any one of claims 14-15, wherein the dynamic offset distance varies with the speed of the mechanism in at least one of the first direction and the second direction.

20. The ultrasonic imaging device according to any one of claims 14-15, further comprising a treatment transducer configured to apply ultrasonic treatment to the tissue.

21. The ultrasonic imaging device according to any one of claims 14-15, wherein N is any one value of 2, 3, or 4.

22. A method for reducing multipath echo artifacts in an ultrasonic image, comprising: Providing an ultrasonic probe, the ultrasonic probe including: An ultrasonic imaging transducer adapted to image a tissue region, A housing, including an acoustic window, A dynamic offset distance between the ultrasonic imaging transducer and the acoustic window, wherein the dynamic offset distance varies over time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, and wherein the first offset distance is different from the second offset distance, An acoustic coupling medium, located within the housing, configured to acoustically couple the ultrasonic imaging transducer to the acoustic window, A motion mechanism for moving the ultrasonic imaging transducer in a first direction and in a second direction, Wherein, when traveling in the first direction, the ultrasonic imaging transducer images in a sequence of focus zones (f1, …, f N ), where N > 2, Wherein, when traveling in the second direction, the ultrasonic imaging transducer images in a second sequence of focus zones (f1, ……, f N ); and Measuring a first offset depth; Calculating a first offset time based on the first offset depth; Multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and Select a pulse repetition interval configured to place the at least one multipath echo artifact outside of the displayed ultrasound image.

23. A method of reducing multipath echo artifacts in an ultrasound image, comprising: Providing an ultrasound probe, the ultrasound probe comprising: An ultrasound imaging transducer adapted to image a tissue region, A housing including an acoustic window, A dynamic offset distance between the ultrasound imaging transducer and the acoustic window, wherein the dynamic offset distance varies over time, wherein the dynamic offset distance includes a first offset distance and a second offset distance, wherein the first offset distance is different from the second offset distance, An acoustic coupling medium located within the housing and configured to acoustically couple the ultrasound imaging transducer to the acoustic window, A motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction; Calculating a first offset time based on the first offset depth; Multiply the first offset time by an integer to determine the presence of the at least one multipath echo artifact; and Select at least one focus zone mixing point configured to place the at least one multipath echo artifact outside of the displayed ultrasound image.

24. The method according to any one of claims 22-23, further comprising: Imaging the tissue, and Displaying the tissue.

25. The method according to any one of claims 22-23, further comprising: Imaging the tissue, and Displaying the tissue, but not treating the tissue.

26. The method according to any one of claims 22-23, further comprising: Treating the tissue.

27. A method of improving ultrasound imaging alignment by reducing spatial and temporal motion artifacts, comprising: Providing an ultrasound probe, the ultrasound probe comprising: An ultrasound imaging transducer adapted to image a tissue region, A motion mechanism attached to the ultrasound imaging transducer; Wherein, when traveling in the first direction, the ultrasonic imaging transducer generates a first image in a sequence of focus zones (f1, …, f N ), where N>2, Wherein, when traveling in the second direction, the ultrasonic imaging transducer generates a second image in a second sequence of focus zones (f1, ……, f N ). Acquiring the first imaging frame; Acquiring the second imaging frame; Calculating an offset between the first imaging frame and the second imaging frame to determine lateral misregistration; Displaying the first imaging frame; and Displaying the second imaging frame, wherein the offset is applied to the second imaging frame to reduce temporal motion artifacts.

28. The method according to claim 27, further comprising: Calculating an optimized image using at least one trigger offset; and Applying the at least one trigger offset to subsequent image acquisitions, wherein the lateral misregistration is reduced due to the application of the at least one trigger offset.

29. A method of improving ultrasound imaging alignment by reducing spatial and temporal motion artifacts, comprising: Providing an ultrasound probe, the ultrasound probe comprising: An ultrasound imaging transducer adapted to image a tissue region, A motion mechanism attached to the ultrasound imaging transducer; Wherein, when traveling in the first direction, the ultrasonic imaging transducer generates a first image in a sequence of focus zones (f1, …, f N ), where N>2, Wherein, when traveling in the second direction, the ultrasonic imaging transducer generates a second image in the order of a second focusing zone sequence (f1, ……, f N ). Acquiring a plurality (N>1) of imaging frames; Calculating a temporal average of at least two imaging frames; Displaying the temporal average of the at least two imaging frames to reduce temporal motion artifacts.

30. The method according to claim 29, further comprising: Calculating an optimized image using at least one trigger offset; and Apply the at least one trigger offset to subsequent image acquisitions, wherein when the spatial misregistration between the current and previously acquired imaging frames is less than a predetermined threshold, the averaging of N>1 consecutive imaging frames can be performed.

31. A method for improving ultrasound imaging alignment by reducing spatial and temporal motion artifacts, comprising: Providing an ultrasound probe, the ultrasound probe comprising: An ultrasound imaging transducer adapted to image a tissue region, A motion mechanism attached to the ultrasound imaging transducer; Wherein, when traveling in the first direction, the ultrasonic imaging transducer generates a first image in a sequence of focus zones (f1, …, f N ), where N>2, Wherein, when traveling in the second direction, the ultrasonic imaging transducer generates a second image in a second focus zone sequence order (f1, ……, f N ). Acquiring the first imaging frame; Acquiring the second imaging frame; Calculating an offset between the first imaging frame and the second imaging frame to determine a lateral misregistration; Calculating a temporal average of the first imaging frame and the second imaging frame; Displaying the temporal average of the first imaging frame and the offset relative to the second imaging frame to reduce spatial and temporal motion artifacts.

32. The method according to claim 31, further comprising: Calculating an optimized image using at least one trigger offset; and Applying the at least one trigger offset to the optimized image, wherein due to the application of the at least one trigger offset, the lateral misregistration is reduced.

33. The method according to any one of claims 27-32, further comprising: Imaging the tissue, and Displaying the tissue.

34. The method according to any one of claims 27-32, further comprising: Imaging the tissue, and Displaying the tissue, but not treating the tissue.

35. The method according to any one of claims 27-32, further comprising treating the tissue.

36. An ultrasound imaging system configured to reduce imaging misalignment, the ultrasound imaging system comprising: An ultrasound probe, the ultrasound probe comprising an ultrasound therapy transducer adapted to apply ultrasound therapy to tissue, an ultrasound imaging transducer adapted to image the tissue, and a motion mechanism for moving the ultrasound imaging transducer in a first direction and in a second direction, wherein the ultrasound imaging transducer is mechanically attached to the motion mechanism, wherein the first direction is opposite to the second direction, Wherein, when traveling in the first direction, the ultrasonic imaging transducer images in a sequence of focus zones (f1, …, f N ), where N>1, Wherein, when traveling in the second direction, the ultrasonic imaging transducer images in a second sequence of focus zones (f1, ……, f N ). wherein the spatial registration between the imaging in the first direction and the imaging in the second direction is improved by staggering trigger positions, Among them, the ultrasonic imaging system adopts direction-related focusing zone sorting (f1,..., f N ) and (f1,..., f N ) on consecutive A-lines; and A control module coupled to the ultrasound probe to control the ultrasound imaging transducer.

37. The method according to claim 36, wherein N = any value in the group consisting of 2, 4, 6, and 8.

38. The ultrasound imaging system according to claim 36, wherein the first direction of movement of the transducer is any one or more directions in the group consisting of a straight line, a rotation, and a curve; wherein the second direction is a reverse path of the first direction.

39. The ultrasound imaging system according to any one of claims 36-38, wherein the ultrasound treatment is at least one of the following treatments: facelift, brow lift, chin lift, eye treatment, wrinkle reduction, improvement of laxity, buttock lift, scar reduction, burn treatment, skin tightening, blood vessel reduction, sweat gland treatment, sunspot removal, fat treatment, cellulite treatment, vaginal tightening, acne treatment, and abdominal laxity treatment.

40. An ultrasound imaging system having one or more of the features described in the foregoing description.

41. A method for reducing imaging misalignment in a mobile ultrasound transducer, having one or more of the features described in the foregoing description.

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