MX367011B

Devices and methods for multi-focus ultrasound therapy.

Abstract

The modalities of a method and system of imaging and dermatological cosmetic treatment may include the use of a transducer to simultaneously or substantially simultaneously produce multiple areas of cosmetic treatment in the tissue. The system may include a hand wand, a removable transducer module, a control module, and a graphical user interface. In some embodiments, the cosmetic treatment system can be used in cosmetic procedures, including eyebrow lift, fat reduction, sweating reduction, and neckline treatment. Skin stretching, lifting and improving wrinkles and stretch marks are provided.

MX367011B, drawing sheet 1 — Sheet 1 of 51

Term

7.4 yearsleft in the term

Expires 28 February 2034.

66 claims: 36 independent, 30 dependent

1
Un sistema de tratamiento estético con ultrasonido para crear simultáneamente múltiples puntos de enfoque con un transductor de ultrasonido, que comprende:una sonda ultrasónica que comprende un transductor de ultrasonido adaptado para aplicar terapia ultrasónica enfocada a tejido en una pluralidad de ubicaciones a una o más profundidades focales con al menos uno del grupo que consiste en modulación de amplitud, polarización, en donde distintos momentos de polarización son proporcionados en una pluralidad de porciones del material piezoeléctrico, y derivación de fase, en donde la pluralidad de porciones del material piezoeléctrico es emitida mediante señales correspondientes con diferentes fases, en donde la pluralidad de porciones del material piezoeléctrico está adaptada para crear variaciones respectivamente en respuesta a un campo eléctrico aplicado al transductor de ultrasonido;y un módulo de control acoplado a la sonda ultrasónica para controlar el transductor de ultrasonido, en donde la pluralidad de ubicaciones se coloca dentro de una zona de tratamiento cosmético, y el transductor de ultrasonido comprende un elemento individual de transducción de ultrasonido, el transductor de ultrasonido estando adaptado para 153 crear múltiples puntos de coagulación termal en el tejido simultáneamente mediante la aplicación del ultrasonido terapéutico, con cada punto de coagulación termal individual separado de los puntos de coagulación termal circundantes por medio de un espaciado de tratamiento.
2
El sistema de tratamiento estético de la reivindicación 1, en donde la pluralidad de ubicaciones se coloca en una secuencia sustancialmente lineal dentro de una zona de tratamiento cosmético y el transductor de ultrasonido comprende un elemento individual de transducción de ultrasonido.
3
El sistema de tratamiento estético de cualquiera de las reivindicaciones anteriores, en donde un primer conjunto de ubicaciones se coloca dentro de una primera zona de tratamiento cosmético y un segundo conjunto de ubicaciones se coloca dentro de una segunda zona de tratamiento cosmético, la primera zona siendo diferente de la segunda zona.
4
El sistema de tratamiento estético de la reivindicación 3, en donde la primera zona de tratamiento cosmético comprende una secuencia sustancialmente lineal del primer conjunto de ubicaciones y la segunda zona de tratamiento cosmético comprende una secuencia sustancialmente lineal del segundo conjunto de ubicaciones.
5
El sistema de tratamiento estético de cualquiera 154 de las reivindicaciones 1 a 4, en donde transductor de ultrasonido está adaptado para aplicar terapia ultrasónica que usa modulación de amplitud por lo que la pluralidad de porciones del transductor de ultrasonido se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud.
6
El sistema de tratamiento estético de cualquiera de las reivindicaciones 1 a 4, en donde el transductor de ultrasonido está adaptado para aplicar derivación de fase de terapia ultrasónica por lo que la pluralidad de porciones del transductor de ultrasonido se adapta para emitir terapia ultrasónica a una pluralidad de fases de intensidad acústica, en donde una primera fase es diferente a una segunda fase.
7
El sistema de tratamiento estético de cualquiera de las reivindicaciones 1 a 4, en donde el transductor de ultrasonido está adaptado para:aplicar terapia ultrasónica que usa modulación de amplitud por lo que la pluralidad de porciones del transductor de ultrasonido se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud;y aplicar derivación de fase de terapia ultrasónica por lo que la pluralidad de porciones del transductor de 155 ultrasonido se adapta para emitir terapia ultrasónica a una pluralidad de fases de intensidad acústica, en donde una primera fase es diferente a una segunda fase.
8
El sistema de tratamiento estético de cualquiera de las reivindicaciones 6 y 7, en donde la pluralidad de fases comprende valores de fase discretos.
9
El sistema de tratamiento estético de cualquiera de las reivindicaciones 5, 7 y 8, en donde el transductor de ultrasonido comprende material piezoeléctrico y la pluralidad de porciones del transductor de ultrasonido está adaptada para crear una pluralidad de variaciones de material piezoeléctrico correspondientes en respuesta a un campo eléctrico aplicado al transductor de ultrasonido.
10
El sistema de tratamiento estético de la reivindicación 9, en donde la pluralidad de variaciones de material piezoeléctrico comprende al menos uno de expansión del material piezoeléctrico y contracción del material piezoeléctrico.
11
El sistema de tratamiento estético de cualquiera de las reivindicaciones 5 y 7 a 10, en donde al menos una porción del transductor ultrasónico está adaptada para emitir terapia ultrasónica en dos o más amplitudes de intensidad acústica, y en donde la amplitud de la terapia ultrasónica emitida por la por lo menos una porción del material 156 piezoeléctrico varía con el paso del tiempo.
12
El sistema de tratamiento estético de cualquiera de las reivindicaciones 1 a 11, que comprende además un mecanismo de movimiento adaptado para que se programe para proporcionar espaciado lineal entre la pluralidad de zonas de tratamiento cosmético individuales.
13
El sistema de tratamiento estético de acuerdo con cualquiera de las reivindicaciones 1 a 11, en donde una secuencia de zonas individuales de tratamiento cosmético tiene un espaciado de tratamiento en un intervalo de aproximadamente 0.01 mm a aproximadamente 25 mm.
14
El sistema de tratamiento estético de acuerdo con cualquiera de las reivindicaciones 1 a 11, en donde el tratamiento ultrasónico está adaptado para al menos uno de una elevación o rejuvenecimiento facial, una elevación de ceja, una elevación de mentón, un tratamiento de ojo, una reducción de arrugas, una reducción de cicatrices, un tratamiento de quemadura, una remoción de tatuaje, un estiramiento de piel, una remoción de venas, una reducción de venas, un tratamiento en una glándula sudorípara, un tratamiento de hiperhidrosis, una remoción de mancha de sol, un tratamiento de grasa, un rejuvenecimiento vaginal y un tratamiento de acné.
15
El sistema de tratamiento estético de cualquiera de las reivindicaciones 1 a 11, en donde el transductor de 157 ultrasonido está adaptado para proporcionar una potencia acústica de la terapia ultrasónica en un intervalo de entre aproximadamente 1W a aproximadamente 100W y una frecuencia de aproximadamente 1 MHz a aproximadamente 10 MHz.
16
Un sistema de tratamiento estético para uso en tratamiento cosmético para crear simultáneamente múltiples puntos focales con un transductor de ultrasonido, el sistema comprendiendo:una sonda ultrasónica que comprende: un primer conmutador que controla de manera operable una función de formación de imágenes ultrasónicas para proporcionar una formación de imágenes ultrasónicas;un segundo conmutador que controla de manera operable una función del tratamiento ultrasónico para proporcionar un tratamiento ultrasónico;y un mecanismo de movimiento adaptado para dirigir el tratamiento ultrasónico en al menos una secuencia de zonas individuales de tratamiento cosmético térmico;y un módulo transductor adaptado para aplicar terapia ultrasónica con al menos uno del grupo que consiste en modulación de amplitud, polarización, en donde distintos momentos de polarización son proporcionados en una pluralidad de porciones de polarización del material piezoeléctrico, y derivación de fase, en donde una pluralidad de porciones de 158 fase del material piezoeléctrico es emitida mediante señales correspondientes con diferentes fases, en donde la pluralidad I de porciones de fase del material piezoeléctrico está adaptada para crear variaciones respectivamente en respuesta a un campo eléctrico aplicado al transductor de ultrasonido, en donde el módulo transductor está adaptado tanto para tratamiento ultrasónico como para formación de imágenes ultrasónicas, en donde el módulo transductor está adaptado para acoplamiento de la sonda ultrasónica, en donde el módulo transductor comprende un transductor de ultrasonido adaptado para aplicar terapia ultrasónica al tejido en una pluralidad de ubicaciones a una o más profundidades focales, en donde el módulo transductor está adaptado para que se acople de manera operable a al menos uno del primer conmutador, el segundo conmutador, y el mecanismo de movimiento;y un módulo de control, en donde el módulo de control comprende un procesador y una pantalla para controlar el módulo transductor.
17
El sistema de tratamiento estético de la reivindicación 16, en donde la pluralidad de ubicaciones se coloca en una secuencia sustancialmente lineal dentro de una 159 zona de tratamiento cosmético.
18
El sistema de tratamiento estético de cualquiera de las reivindicaciones 16 a 17, en donde un primer conjunto de ubicaciones se coloca dentro de una primera zona de tratamiento cosmético y un segundo conjunto de ubicaciones se coloca dentro de una segunda zona de tratamiento cosmético, la primera zona siendo diferente a la segunda zona.
19
El sistema de tratamiento estético de la reivindicación 18, en donde la primera zona de tratamiento cosmético comprende una secuencia sustancialmente lineal del primer conjunto de ubicaciones y la segunda zona de tratamiento cosmético comprende una secuencia sustancialmente lineal del segundo conjunto de ubicaciones.
20
El sistema de tratamiento estético de cualquiera de las reivindicaciones 16 a 19, en donde el módulo transductor está adaptado para aplicar terapia ultrasónica que usa modulación de amplitud por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud.
21
El sistema de tratamiento estético de cualquiera de las reivindicaciones 16 a 20, en donde el módulo transductor está adaptado para aplicar derivación de fase de terapia 160 ultrasónica por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia- ultrasónica a una pluralidad de fases de intensidad acústica, en donde una primera fase es diferente a una segunda fase.
22
El sistema de tratamiento estético de cualquiera de las reivindicaciones 16 a 21, en donde el módulo transductor está adaptado para:aplicar terapia ultrasónica que usa modulación de amplitud por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud;y aplicar derivación de fase de terapia ultrasónica por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia ultrasónica a una pluralidad de fases de intensidad acústica, en donde una primera fase es diferente a una segunda fase.
23
El sistema de tratamiento estético de cualquiera de las reivindicaciones 21 y 22, en donde la pluralidad de fases comprende valores de fase discretos.
24
El sistema de tratamiento estético de cualquiera de las reivindicaciones 20, 22 y 23, en donde el módulo transductor comprende material piezoeléctrico y la pluralidad de porciones del módulo transductor está adaptada para crear 161 una pluralidad de variaciones de material piezoeléctrico correspondientes en respuesta a un campo eléctrico aplicado al módulo transductor.
25
El sistema de tratamiento estético de la reivindicación 24, en donde la pluralidad de variaciones de material piezoeléctrico comprenden al menos uno de expansión del material y contracción del material.
26
El sistema de tratamiento estético de cualquiera de las reivindicaciones 20 y 22 a 25, en donde al menos una porción del módulo transductor está adaptado para emitir terapia ultrasónica a dos o más amplitudes de intensidad acústica, y en donde la amplitud de la terapia ultrasónica emitida por la al menos una porción del módulo transductor varía con el paso del tiempo.
27
El sistema de tratamiento estético de cualquiera de las reivindicaciones 16 a 26, en donde el mecanismo de movimiento está adaptado para que se programe para proporcionar espaciado variable entre una pluralidad de zonas individuales de tratamiento cosmético térmico.
28
El sistema de tratamiento estético de acuerdo con cualquiera de las reivindicaciones 16 a 26, en donde una secuencia de zonas individuales de tratamiento cosmético térmico tiene un espaciado de tratamiento en el intervalo de aproximadamente 0.01 mm a aproximadamente 25 mm. 162
29
El sistema de tratamiento estético de acuerdo con cualquiera de las reivindicaciones 16 a 26, en donde el primer y segundo conmutadores comprenden teclas o botones operados por usuario.
30
El sistema de tratamiento estético de acuerdo con cualquiera de las reivindicaciones 16 a 26, en donde al menos uno del primer conmutador y el segundo conmutador se activa por medio del módulo de control.
31
El sistema de tratamiento estético de acuerdo con cualquiera de las reivindicaciones 16 a 26, en donde la función de tratamiento se adapta para al menos una de una elevación o rejuvenecimiento facial, una elevación de ceja, una elevación de mentón, un tratamiento de ojo, una reducción de arrugas, una reducción de cicatrices, un tratamiento de quemadura, una remoción de tatuaje, un estiramiento de piel, una remoción de vena, una reducción de vena, un tratamiento en una glándula sudorípara, un tratamiento de hiperhidrosis, una remoción de mancha de sol, un tratamiento de grasa, un rejuvenecimiento vaginal y un tratamiento de acné.
32
El sistema de tratamiento estético de cualquiera de las reivindicaciones 16 a 26, en donde el módulo transductor está adaptado para proporcionar una potencia acústica de la terapia ultrasónica en el intervalo de entre aproximadamente 1W a aproximadamente 100W y una frecuencia de aproximadamente 163 1 MHz a aproximadamente 10 MHz.
33
Un sistema de tratamiento, el sistema comprendiendo:un dispositivo de control que controla de manera operable una función de tratamiento ultrasónico para proporcionar un tratamiento ultrasónico simultáneamente en dos o más ubicaciones;y una varita de mano adaptada para dirigir el tratamiento ultrasónico en una secuencia de zonas individuales de tratamiento cosmético térmico, la varita de mano comprendiendo: un transductor adaptado para aplicar terapia ultrasónica a tejido en una ubicación a una o más profundidades focales, la ubicación colocada dentro de una zona de tratamiento cosmético térmico, en donde el transductor está adaptado adicionalmente para aplicar terapia ultrasónica al tejido simultáneamente en una pluralidad de ubicaciones a la profundidad focal con polarización, en donde distintos momentos de polarización son proporcionados en una pluralidad de porciones de polarización del material piezoeléctrico, y derivación de fase, en donde una pluralidad de porciones de fase del material piezoeléctrico es emitida mediante señales correspondientes con diferentes fases, en donde la pluralidad de porciones de fase del material 164 piezoeléctrico están adaptadas para crear variaciones respectivamente en respuesta a un campo eléctrico aplicado al transductor de ultrasonido.
34
Un sistema de tratamiento estético para crear simultáneamente múltiples puntos focales en tejido con un transductor de ultrasonido, el sistema comprendiendo:un dispositivo de control que controla de manera operable una función de tratamiento ultrasónico para proporcionar un tratamiento ultrasónico;y una varita de mano adaptada para dirigir el tratamiento ultrasónico en una secuencia de zonas individuales del tratamiento cosmético térmico, la varita de mano comprendiendo: un transductor individual adaptado para aplicar simultáneamente terapia ultrasónica a tejido en una pluralidad de ubicaciones a una profundidad focal con al menos uno del grupo que consiste en modulación de amplitud y polarización, en donde diferentes momentos de polarización se proporcionan en una pluralidad de porciones del material piezoeléctrico.
35
Un sistema de formación de imágenes y tratamiento estético para el uso en un tratamiento cosmético, el sistema comprendiendo:una sonda ultrasónica adaptada para tratamiento ultrasónico y formación de imágenes ultrasónicas de tejido en 165 una pluralidad de ubicaciones a una profundidad focal, que comprende: un módulo transductor adaptado para acoplarse a la sonda ultrasónica, en donde el módulo transductor comprende un transductor de ultrasonido adaptado para aplicar una terapia ultrasónica a tejido en la pluralidad de ubicaciones a la profundidad focal, con al menos uno del grupo que consiste en polarización, en donde distintos momentos de polarización son proporcionados en una pluralidad de porciones del material piezoeléctrico, y derivación de fase, en donde la pluralidad de porciones del material piezoeléctrico es emitida mediante señales correspondientes con diferentes fases, en donde la pluralidad de porciones del material piezoeléctrico está adaptada para crear variaciones respectivamente en respuesta a un campo eléctrico aplicado al transductor de ultrasonido, un primer conmutador que controla de manera operable una función de formación de imágenes ultrasónicas para proporcionar formación de imágenes ultrasónicas;un segundo conmutador que controla de manera operable una función del tratamiento ultrasónico para proporcionar la terapia ultrasónica;y un mecanismo de movimiento adaptado para dirigir el tratamiento ultrasónico en al menos una secuencia de zonas 166 individuales de tratamiento cosmético térmico;y en donde el módulo transductor está adaptado para que se acople de manera operable a al menos uno del primer conmutador, el segundo conmutador y el mecanismo de movimiento;y un módulo de control, en donde el módulo de control comprende un procesador y una pantalla para controlar el módulo transductor.
36
El sistema de formación de imágenes y tratamiento estético de la reivindicación 35, en donde la pluralidad de ubicaciones está colocada en una secuencia sustancialmente lineal dentro de una zona de tratamiento cosmético.
37
El sistema de formación de imágenes y tratamiento estético de la reivindicación 35, en donde un primer conjunto de ubicaciones se coloca dentro de una primera zona de tratamiento cosmético y un segundo conjunto de ubicaciones se coloca dentro de una segunda zona de tratamiento cosmético, la primera zona siendo diferente a la segunda zona.
38
El sistema de formación de imágenes y tratamiento estético de la reivindicación 35, en donde la primera zona de tratamiento cosmético comprende una secuencia sustancialmente lineal del primer conjunto de ubicaciones y la segunda zona de tratamiento cosmético comprende una secuencia 167 sustancialmente lineal del segundo conjunto de ubicaciones.
39
El sistema de formación de imágenes y tratamiento estético de la reivindicación 35, en donde el módulo transductor está adaptado para aplicar terapia ultrasónica que usa modulación de amplitud por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud. 40. El sistema de formación de imágenes y tratamiento estético de la reivindicación 35, en donde el módulo transductor está adaptado para aplicar derivación de fase de terapia ultrasónica por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia ultrasónica en una pluralidad de fases de intensidad acústica, en donde una primera fase es diferente a una segunda fase.
40
41. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 35 a 40, en donde el módulo transductor está adaptado para:aplicar terapia ultrasónica que usa modulación de amplitud por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud;y 168 aplicar derivación de fase de terapia ultrasónica por lo que una pluralidad de porciones del módulo transductor se adapta para emitir terapia ultrasónica en una pluralidad de fases de intensidad acústica, en donde una primera fase es diferente a una segunda fase.
41
42. El sistema de formación de imágenes y tratamiento estético de la reivindicación 41, en donde la pluralidad de fases comprende valores de fase discretos.
42
43. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 35 a 40, en donde el módulo transductor comprende material piezoeléctrico y la pluralidad de porciones del módulo transductor se adapta para crear una pluralidad de variaciones correspondientes del material piezoeléctrico en respuesta a un campo eléctrico aplicado al módulo transductor.
43
44. El sistema de formación de imágenes y tratamiento estético de la reivindicación 43, en donde la pluralidad de variaciones de material piezoeléctrico comprende al menos uno de expansión del material y contracción del material.
44
45. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 35 a 40, en donde al menos una porción del módulo transductor está adaptada para emitir terapia ultrasónica a dos o más amplitudes 169 de intensidad acústica, y en donde la amplitud de la terapia ultrasónica emitida por la al menos una porción del módulo transductor varia con el paso del tiempo.
45
46. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 35 a 40, en donde el mecanismo de movimiento está adaptado para programarse y para proporcionar espaciado variable entre una pluralidad de zonas individuales de tratamiento cosmético térmico.
46
47. El sistema de formación de imágenes y tratamiento estético de acuerdo con cualquiera de las reivindicaciones 35 a 40, en donde una secuencia de zonas individuales de tratamiento cosmético térmico tiene un espaciado de tratamiento en un intervalo de aproximadamente 0.01 mm a aproximadamente 25 mm.
47
48. El sistema de formación de imágenes y tratamiento estético de acuerdo con cualquiera de las reivindicaciones 35 a 40, en donde el primer y segundo conmutadores comprenden teclas o botones operados por usuario.
48
49. El sistema de formación de imágenes y tratamiento estético de acuerdo con cualquiera de las reivindicaciones 35 a 40, en donde al menos uno del primer conmutador y el segundo conmutador se activa por medio del módulo de control. 170
49
50. El sistema de formación de imágenes y tratamiento estético de acuerdo con cualquiera de las reivindicaciones 35 a 40, en donde la función de tratamiento se adapta para al menos una de una elevación o rejuvenecimiento facial, una elevación de ceja, una elevación de mentón, un tratamiento de ojo, una reducción de arrugas, una reducción de cicatrices, un tratamiento de quemadura, una remoción de tatuaje, un estiramiento de piel, una remoción de vena, una reducción de vena, un tratamiento en una glándula sudorípara, un tratamiento de hiperhidrosis, una remoción de mancha de sol, un tratamiento de grasa, un rejuvenecimiento vaginal y un tratamiento de acné.
50
51. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 35 a 40, en donde el módulo transductor está adaptado para proporcionar una potencia acústica de la terapia ultrasónica en un intervalo de entre aproximadamente 1W a aproximadamente 100W y una frecuencia de aproximadamente 1 MHz a aproximadamente 10 MHz. 52. Un sistema de tratamiento de ultrasonido multifocal simultáneo, el sistema comprendiendo:un dispositivo de control que controla de manera operable una función de tratamiento ultrasónico para proporcionar un tratamiento ultrasónico;y 171 una varita de mano adaptada para dirigir el tratamiento ultrasónico en una secuencia de zonas individuales de tratamiento cosmético térmico, la varita de mano comprendiendo: un transductor adaptado para aplicar terapia ultrasónica a tejido en una ubicación a una profundidad focal, la ubicación colocada dentro de una zona de tratamiento cosmético térmico, en donde el transductor está adaptado adicionalmente para aplicar terapia ultrasónica a tejido de manera simultánea en una pluralidad de ubicaciones a la profundidad focal con modulación de amplitud, polarización, en donde distintos momentos de polarización son proporcionados en una pluralidad de porciones del material piezoeléctrico, y derivación de fase, en donde la pluralidad de porciones del material piezoeléctrico es emitida mediante señales correspondientes con diferentes fases, en donde la pluralidad de porciones del material piezoeléctrico está adaptada para crear variaciones respectivamente en respuesta a un campo eléctrico aplicado al transductor de ultrasonido.
51
53. Un sistema de tratamiento multifocal simultáneo y formación de imágenes estético, que comprende:un módulo que comprende un transductor de ultrasonido, 172 en donde el transductor de ultrasonido está adaptado para aplicar terapia ultrasónica a tejido en una pluralidad de ubicaciones a una profundidad focal con al menos uno del grupo que consiste en modulación de amplitud, polarización, en donde distintos momentos de polarización son proporcionados en una pluralidad de porciones del material piezoeléctrico, y derivación de fase, en donde la pluralidad de porciones del material piezoeléctrico es emitida mediante señales correspondientes con diferentes fases, en donde la pluralidad de porciones del material piezoeléctrico está adaptada para crear variaciones respectivamente en respuesta a un campo eléctrico aplicado al transductor de ultrasonido, en donde el módulo comprende además una guia de interconexión diseñada para acoplarse de manera removible a una varita de mano para proporcionar comunicación electrónica y energía entre el módulo y la varita de mano.
52
54. El sistema de formación de imágenes y tratamiento estético de la reivindicación 53, en donde la pluralidad de ubicaciones están colocadas en una secuencia sustancialmente lineal dentro de una zona de tratamiento cosmético.
53
55. El sistema de formación de imágenes y tratamiento estético de la reivindicación 53, en donde un primer conjunto de ubicaciones se coloca dentro de una primera 173 zona de tratamiento cosmético y un segundo conjunto de ubicaciones se coloca dentro de una segunda zona de tratamiento cosmético, la primera zona siendo diferente a la segunda zona.
54
56. El sistema de formación de imágenes y tratamiento estético de la reivindicación 55, en donde la primera zona de tratamiento cosmético comprende una secuencia sustancialmente lineal del primer conjunto de ubicaciones y la segunda zona de tratamiento cosmético comprende una secuencia sustancialmente lineal del segundo conjunto de ubicaciones.
55
57. El sistema de formación de imágenes y tratamiento estético de la reivindicación 53, en donde el transductor de ultrasonido está adaptado para aplicar terapia ultrasónica que usa modulación de amplitud por lo que una pluralidad de porciones del transductor de ultrasonido se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud.
56
58. El sistema de formación de imágenes y tratamiento estético de la reivindicación 53, en donde el transductor de ultrasonido está adaptado para aplicar derivación de fase de terapia ultrasónica por lo que una pluralidad de porciones del transductor de ultrasonido se adapta para emitir terapia ultrasónica en una pluralidad de fases de intensidad acústica, en donde una primera fase es 174 diferente a una segunda fase.
57
59. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 53 a 58, en donde el transductor de ultrasonido está adaptado para:aplicar terapia ultrasónica que usa modulación de amplitud por lo que una pluralidad de porciones del transductor de ultrasonido se adapta para emitir terapia ultrasónica en una pluralidad de amplitudes de intensidad acústica, en donde una primera amplitud es diferente a una segunda amplitud;y aplicar derivación de fase de terapia ultrasónica por lo que una pluralidad de porciones del transductor de ultrasonido se adapta para emitir terapia ultrasónica a una pluralidad de fases de intensidad acústica, en donde una primera fase es diferente a una segunda fase.
58
60. El sistema de formación de imágenes y tratamiento estético de la reivindicación 59, en donde la pluralidad de fases comprende valores discretos de fase.
59
61. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 53 a 58, en donde el transductor de ultrasonido comprende el material piezoeléctrico y la pluralidad de porciones del transductor de ultrasonido está adaptada para crear una pluralidad de variaciones del material piezoeléctrico 175 correspondientes en respuesta a un campo eléctrico aplicado al transductor de ultrasonido.
60
62. El sistema de formación de imágenes y tratamiento estético de la reivindicación 61, en donde la pluralidad de variaciones del material piezoeléctrico comprenden al menos una de expansión del material piezoeléctrico y contracción del material piezoeléctrico.
61
63. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 53 a 58, en donde al menos una porción del transductor ultrasónico está adaptada para emitir terapia ultrasónica en dos o más amplitudes de intensidad acústica, y en donde la amplitud de la terapia ultrasónica emitida por la al menos una porción del material piezoeléctrico varía con el paso del tiempo.
62
64. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 53 a 58, que comprende además un mecanismo de movimiento adaptado para que se programe para proporcionar espaciado entre la pluralidad de zonas individuales de tratamiento cosmético.
63
65. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 53 a 58, en donde una secuencia de zonas individuales de tratamiento cosmético tiene un espaciado de tratamiento en un intervalo de entre aproximadamente 0.01 mm a aproximadamente 176 25 mm.
64
66. El sistema de formación de imágenes y tratamiento estético de acuerdo con cualquiera de las reivindicaciones 53 a 58, en donde el transductor de ultrasonido se adapta para al menos uno de una elevación o rejuvenecimiento facial, una elevación de ceja, una elevación de mentón, un tratamiento de ojo, una reducción de arrugas, una reducción de cicatrices, un tratamiento de quemadura, una remoción de tatuaje, un estiramiento de piel, una remoción de vena, una reducción de vena, un tratamiento en una glándula sudorípara, un tratamiento de hiperhidrosis, una remoción de mancha de sol, un tratamiento de grasa, un rejuvenecimiento vaginal y un tratamiento de acné.
65
67. El sistema de formación de imágenes y tratamiento estético de cualquiera de las reivindicaciones 53 a 58, en donde el transductor de ultrasonido está adaptado para proporcionar una potencia acústica de la terapia ultrasónica en el intervalo de entre aproximadamente 1W a aproximadamente 100W y una frecuencia de aproximadamente 1 MHz a aproximadamente 10 MHz.
66
68. Un sistema de tratamiento, el sistema comprendiendo:un dispositivo de control que controla de manera operable una función de tratamiento ultrasónico para

Independent claims66

393 paragraphs in 2 sections, as filed

DEVICES AND METHODS FOR MULTIFOCAL ULTRASOUND THERAPY

Referral to Related Requests [0001] This application claims the priority benefit of provisional application US No. 61 / 774,785 filed on March 8, 2013, which is incorporated in its entirety by reference, herein.

Field of the Invention [0002] Several embodiments of the present invention generally refer to non-invasive energy-based treatments to achieve cosmetic effects. For example, some modalities generally refer to devices, systems and methods for providing multiple ultrasound treatment points or focus areas to perform various processing and / or imaging processes in a safe and effective manner. Some modalities refer to the division of a beam of ultrasound therapy into two, three, four or more focal areas to perform various processing and / or imaging with multiple phases and / or modulated phases. Some modalities refer to the division of a beam of ultrasound therapy into two, three, four or more focal areas to perform various processing and / or imaging with polarization techniques. In various modalities, devices and methods are provided to direct ultrasound therapy to multiple focus points in cosmetic and / or medical processing.

Background of the Invention [0003] Many cosmetic procedures include invasive processes that may require invasive surgery. Patients not only have to resist weeks of recovery time, but they are also frequently required to undertake risky anesthesia procedures for aesthetic treatments.

Brief Description of the Invention [0004] Although energy-based treatments have been described for cosmetic and medical purposes, no procedure, other than the applicant's own work, which successfully achieves an aesthetic effect using directed ultrasound is known to the applicant. and precise to cause a visible and effective cosmetic result by a thermal route by dividing an ultrasound therapy beam to two, three, four or more focal areas to perform various treatment and / or imaging procedures.

[0005] In several embodiments described herein, non-invasive ultrasound is used to achieve one or more of the following effects: a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a tattoo removal, a vein removal, a vein reduction , a treatment in a sweat gland, a hyperhidrosis treatment, a sunspot removal, an acne treatment, a reduction of pimples. Neckline treatment is provided in several modalities. In another embodiment, the device can be used in adipose tissue (for example, fat). In another embodiment, the system, device and / or method may be applied in the genital area (for example, vaginal rejuvenation and / or vaginal narrowing, such as to narrow the supportive tissue of the vagina).

[0006] According to several modalities, a system and / or method of cosmetic ultrasound treatment can non-invasively produce a zone or multiple zones of cosmetic treatment with one or multiple coagulation points.

<td colspan="2">thermal where</td><td>I know</td><td>focus</td><td>the ultrasound in a</td><td>or more</td>

<td>locations</td><td>in</td><td>a</td><td>region of</td><td>tissue treatment</td><td>under the</td>

<td>surface</td><td>from</td><td>the</td><td>skin.</td><td>Some systems and</td><td>methods</td>

They provide cosmetic treatment at different locations in the tissue, such as at different depths, heights, widths and / or positions. In one embodiment, a system and method comprises a multi-depth transducer system configured to provide ultrasound treatment to more than one region of interest, such as between at least two of a deep treatment region of interest, a surface region of interest and / or a subcutaneous region of interest. In one embodiment, a method and system comprise a transducer system configured to provide ultrasound treatment to more than one region of interest, such as between at least two points in various locations (for example, at a depth, height, width, fixed orientation or variable, etc.) in a region of interest in the tissue. Some modalities may divide a beam to focus on two, three or four or more focal points (for example, multiple focal points, or multifocal points) for cosmetic treatment areas and / or for imaging a region of interest in the tissue. . The position of the focal points can be placed axially, laterally or otherwise within the tissue. Some modalities for spatial control can be configured, such as by the location of a focus point, changing the distance of a transducer to a reflection surface, and / or changing the angles of energy focused or not focused on the region of interest and / or configured for temporary control, such as controlling changes in frequency, drive amplitude and transducer synchronization. In some modalities, the position of the multiple treatment zones or focal points with polarization, phase polarization, biphasic polarization and / or multiphasic polarization. In some modalities, the position of the multiple treatment zones or focal points with fascination, such as in one modality, electric fascination. As a result, changes in the location of the treatment region, the number, shape, size and / or volume of the treatment areas or lesions in a region of interest can be dynamically controlled over time, as well as thermal conditions

[0007] According to several modalities, a system and / or method of cosmetic ultrasound treatment can create multiple zones of cosmetic treatment using one or more phase modulation, polarization, non-linear acoustics, and / or Fourier transforms to create some periodic spatial pattern with one or multiple portions of ultrasound. In one embodiment, a system simultaneously or sequentially distributes one or multiple treatment zones using polarization at a certain level. In one embodiment, a polarization pattern is a function of local frequency and depth, and the use of odd or even functions. In one embodiment, a process in two or more dimensions can be used to create any periodic spatial pattern. In one embodiment, an ultrasound beam is divided axially and laterally to significantly reduce the treatment time through the use of non-linear Fourier and acoustic transforms. In one embodiment, modulation of a system and amplitude modulation of a ceramic product or transducer can be used to place multiple treatment zones in the tissue, either sequentially or simultaneously.

[0008] In one embodiment, an imaging and aesthetic treatment system includes an ultrasonic zone that includes an ultrasound transducer configured to apply ultrasonic therapy to the tissue in a plurality of locations at a focal depth with at least one of the group consisting of phase variation and polarization by amplitude modulation. In one embodiment, the system includes a control module coupled to the ultrasound zone to control the ultrasound transducer.

[0009] In several embodiments, the plurality of locations are placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second set of locations is placed within a second cosmetic treatment zone, the first zone that is different from the second zone. In one embodiment, the first cosmetic treatment zone includes a substantially linear sequence of the first set of locations and the second cosmetic treatment zone includes a substantially linear sequence of the second set of locations. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby a plurality of portions of the ultrasound transducer are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy phase variation whereby a plurality of portions of the ultrasound transducer are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, whereby a first phase It is different from a second phase. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby it is configured in a plurality of portions of the ultrasound transducer to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude It is different from a second amplitude, and applying phase variation of ultrasonic therapy whereby a plurality of portions of the ultrasound transducer are configured to emit ultrasonic therapy to a plurality of phases of acoustic intensity, wherein a first phase is different from a second phase. In one embodiment, the plurality of phases includes discrete phase values. In one embodiment, the ultrasound transducer includes piezoelectric material and the plurality of portions of the ultrasound transducer is configured to create a plurality of corresponding variations of piezoelectric material in response to an electric field applied to the ultrasound transducer. In one embodiment, the plurality of variations of piezoelectric material includes at least one of expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, at least a portion of the ultrasound transducer is configured to emit ultrasonic therapy at two or more amplitudes of acoustic intensity, and where the amplitude of the ultrasonic therapy emitted by at least a portion of the piezoelectric material varies with the passage of the weather. In one embodiment, the system also includes a movement mechanism configured to be programmed to provide variable spacing between the plurality of individual cosmetic treatment zones. In one embodiment, a sequence of individual cosmetic treatment zones has a treatment spacing in a range of about O. mm to about 25 mm. In several embodiments, the ultrasonic treatment is at least one of a face lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a removal of tattoo, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation and an acne treatment. In one embodiment, the ultrasound transducer is configured to provide an acoustic power of the ultrasonic therapy in a range of between about 1W to about 100W and a frequency of about 1 MHz to about 10 MHz to heat the tissue thermally to cause coagulation.

[00010] In one embodiment, an imaging and aesthetic treatment system for use in cosmetic treatment includes: an ultrasonic zone and a control module. The ultrasonic zone includes a first switch that operably controls an ultrasonic imaging function to provide ultrasonic imaging, a second switch that operably controls an ultrasonic treatment function to provide an ultrasonic treatment and a motion mechanism configured to direct the ultrasonic treatment in at least one sequence of individual zones of thermal cosmetic treatment. In one embodiment, the system also includes a transducer module. In one embodiment, the transducer module is configured both to form ultrasonic images and for ultrasonic treatment. In one embodiment, the transducer module is configured for coupling to the ultrasonic probe. In one embodiment, the transducer module includes an ultrasound transducer configured to apply ultrasonic therapy to tissue in a plurality of locations at a focal depth. In one embodiment, the transducer module is configured to operably couple at least one of the first switch, the second switch and the movement mechanism. In one embodiment, the control module includes a processor and display to control the transducer module.

[00011] In several embodiments, the plurality of locations are placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second set of locations is placed within a second cosmetic treatment zone, the first zone that is different from the second zone. In one embodiment, the first cosmetic treatment zone includes a substantially linear sequence of the first set of locations and the second cosmetic treatment zone includes a substantially linear sequence of the second set of locations. In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude modulation so it is configured in a plurality of portions of the transducer module to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, where a first amplitude is different. of a second amplitude. In one embodiment, the transducer module is configured to apply ultrasonic therapy phase variation whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, wherein a first phase is different from A second phase In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude modulation so it is configured in a plurality of portions of the transducer module to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, where a first amplitude is different. of a second amplitude. In one embodiment, the transducer module is configured to apply ultrasonic therapy phase variation so it is configured in a plurality of portions of the transducer module to emit ultrasonic therapy to a plurality of acoustic intensity phases, where a first phase is different. of a second phase. In one embodiment, the plurality of phases includes discrete phase values. In one embodiment, the transducer module is configured such that the transducer module includes piezoelectric material and the plurality of portions of the transducer module are configured to create a plurality of corresponding variations of the piezoelectric material in response to an electric field applied to the transducer module. In one embodiment, the plurality of variations of piezoelectric material includes at least one of material expansion and material contraction. In one embodiment, at least a portion of the transducer module is configured to emit ultrasonic therapy at two or more amplitudes of acoustic intensity, and wherein the amplitude of ultrasonic therapy emitted by at least a portion of the transducer module varies with the passage of the weather. In one embodiment, the movement mechanism is configured to be programmed to provide variable spacing between a plurality of individual zones of thermal cosmetic treatment. In one embodiment, a sequence of individual zones of thermal cosmetic treatment has a treatment spacing in a range of about 0.01 mm to about 25 mm. In one mode the first and second switches include keys or buttons operated by user. In one mode, at least one of the first switch and the second switch is activated by the control module. In one embodiment, the treatment function is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a tattoo removal, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation and an acne treatment. In one embodiment, the transducer module is configured to provide an acoustic power of the ultrasonic therapy in a range of between about 1W to about 100W and a frequency of about 1 MHz to about 10 MHz to heat the tissue thermally to cause coagulation.

[00012] In one embodiment, a treatment system includes a control device that operably controls an ultrasonic therapy function to provide an ultrasonic treatment and a hand wand configured to direct the ultrasonic treatment in a sequence of individual treatment zones. Cosmetic, thermal In one embodiment, the hand wand includes a transducer configured to apply ultrasonic therapy to the tissue at a location at a focal depth, the location placed within a cosmetic, thermal treatment zone, where the transducer is further configured to apply ultrasonic therapy. to the tissue in a plurality of locations at the focal depth.

[00013] In one embodiment, a method for performing cosmetic processing includes coupling a transducer module with an ultrasonic probe, wherein the ultrasonic probe includes a first switch to control the formation of acoustic images, wherein the ultrasonic probe includes a second switch. to control acoustic therapy to cause a plurality of individual areas of cosmetic treatment, wherein the acoustic probe includes a movement mechanism to provide desired spacing between individual areas of cosmetic treatment. In one embodiment, the method includes contacting the transducer module with the skin surface of a subject. In one embodiment, the method includes activating the first switch in the acoustic probe to image acoustically, with the transducer module, a region below the surface of the skin. In one embodiment, the method includes activating the second switch in the acoustic probe to acoustically treat, with the transducer module, the region below the surface of the skin in a desired sequence of individual areas of cosmetic treatment that is controlled by the movement mechanism, wherein the transducer module includes an ultrasound transducer configured to apply ultrasonic therapy to the tissue in a plurality of locations at a focal depth.

[00014] In one embodiment, a treatment system includes a control device that operably controls an ultrasonic treatment function to provide ultrasonic treatment, and a hand wand configured to direct the ultrasonic treatment in a sequence of individual zones of cosmetic, thermal treatment. In one embodiment, the hand wand includes a transducer configured to apply ultrasonic therapy to the tissue in a plurality of locations at a focal depth.

[00015] In one embodiment, the use of an imaging system and aesthetic treatment for the non-invasive cosmetic treatment of the skin.

[00016] According to several modalities, An aesthetic ultrasound treatment system for creating multiple focus points with an ultrasound transducer includes an ultrasonic probe comprising an ultrasound transducer includes an ultrasonic probe comprising an ultrasound transducer configured to apply ultrasonic therapy to the tissue in a plurality of locations at a focal depth with at least one of the group consisting of amplitude modulation polarization and phase variation, and a control module coupled to the ultrasonic probe to control the ultrasound transducer.

[00017] In one embodiment, the ultrasound treatment comprises an individual ultrasound transduction element. In one embodiment, the plurality of locations are placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second set of locations is placed within a second cosmetic treatment zone, the first zone being different from the first zone. In one embodiment, the first cosmetic treatment zone comprises a substantially linear sequence of the first set of locations and the second cosmetic treatment zone comprises a substantially linear sequence of the second set of locations.

[00018] In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby it is configured in a plurality of portions of the ultrasound transducer to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein A first amplitude is different from a second amplitude. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy phase variation so it is configured in a plurality of portions of the ultrasound treatment to emit ultrasonic therapy to a plurality of acoustic intensity phases, where a first phase It is different from a second phase. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby it is configured in a plurality of portions of the ultrasound transducer to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude It is different from a second amplitude, and applying the phase variation from ultrasonic therapy whereby a plurality of portions of the ultrasound transducer are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the ultrasound transducer comprises piezoelectric material and the plurality of portions of the ultrasound transducer is configured to create a plurality of corresponding variations of piezoelectric material in response to an electric field applied to the ultrasound transducer. In one embodiment, the plurality of variations of piezoelectric material comprises at least one of expansion of piezoelectric material and contraction of piezoelectric material. In one embodiment, at least a portion of the ultrasound transducer is configured to emit ultrasonic therapy at two or more amplitudes of acoustic intensity, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the piezoelectric material varies with the passage of the weather.

[00019] In one embodiment, the system also includes a movement mechanism configured to be programmed to provide variable spacing between the plurality of individual areas of cosmetic treatment. In one embodiment, a sequence of individual cosmetic treatment zones has a treatment spacing in a range of about 0.01 mm to about 25 mm.

[00020] In several embodiments, the ultrasonic treatment is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment , a tattoo removal, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation and an acne treatment.

[00021] In one embodiment, the ultrasonic transducer is configured to provide an acoustic power of the ultrasonic therapy in a range of between about 1W to about 100W and a frequency of about 1 MHz to about 10 MHz to heat treat the tissue to cause coagulation. .

[00022] According to several modalities, a cosmetic treatment system for use in cosmetic treatment to create multiple focal points with an ultrasound transducer includes an ultrasonic probe that includes a first switch that operably controls a function of forming a ultrasonic images to provide ultrasonic imaging, a second switch that operably controls an ultrasonic treatment function to provide an ultrasonic treatment and a movement mechanism configured to direct the ultrasonic treatment in at least one sequence of the individual zones of the cosmetic, thermal treatment. The system includes a transducer module configured to apply ultrasonic therapy with at least one of the group consisting of amplitude modulation polarization and phase variation, where the transducer module is configured for both ultrasonic imaging and ultrasonic treatment, where The transducer module is configured for coupling to the ultrasonic probe, wherein the transducer module comprises an ultrasound transducer configured to apply ultrasonic therapy to the tissue in a plurality of locations at a focal depth, wherein the transducer module is configured to be operably coupled with at least one of the first switch, the second switch and the movement mechanism, and a control module, wherein the control module comprises a processor and a screen for controlling the transducer module.

[00023] In one embodiment, the plurality of locations are placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second set of locations is placed within a second cosmetic treatment zone, the first zone that is different from the second zone. In one embodiment, the first cosmetic treatment zone comprises a substantially linear sequence of the first set of locations and the second cosmetic treatment zone comprises a substantially linear sequence of the second set of locations.

[00024] In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude module so it is configured in a plurality of portions of the transducer module to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the transducer module is configured to apply ultrasonic therapy phase variation whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, wherein a first phase is different from A second phase In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude modulation whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude and apply phase variation of ultrasonic therapy whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, where a first phase is different from a second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the transducer module comprises piezoelectric material and the plurality of portions of the transducer module are configured to create a plurality of corresponding variations of the piezoelectric material in response to an electric field applied to the transducer module. In one embodiment, the plurality of variations of piezoelectric material comprises at least one of material expansion and material contraction. In one embodiment, at least a portion of the transducer module is configured to emit ultrasonic therapy at two or more amplitudes of acoustic intensity, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the transducer module varies with the step weather.

[00025] In one embodiment, the movement mechanism is configured to be programmed to provide variable spacing between a plurality of individual zones of cosmetic, thermal treatment. In one embodiment, a sequence of individual cosmetic, thermal treatment zones has a treatment spacing in a range of about 0.01 mm to about 25 mm. In one embodiment, the first and second switches comprise keys or buttons operated by user. In one mode, at least one of the first switch and the second switch are activated by the control module.

[00026] In one embodiment, the treatment function is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a treatment of sunburn, a tattoo removal, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation and an acne treatment.

[00027] In one embodiment, the transducer module is configured to provide an acoustic power of the ultrasonic therapy in a range of between approximately

1W to about 100W and a frequency of about 1 MHz to about 10 MHz to heat the tissue thermally to cause clotting.

[00028] According to several modalities, a treatment system includes a control device that operably controls an acoustic treatment function to provide an ultrasonic treatment, and a hand wand to direct the ultrasonic treatment in a sequence of individual zones. of cosmetic, thermal treatment. The hand wand includes a transducer configured to apply ultrasonic therapy to tissue at a location at a focal depth. The location placed within a cosmetic, thermal treatment zone, where the transducer is further applied to apply ultrasonic therapy to the tissue in a plurality of locations at the focal depth.

[00029] According to several modalities, a method for performing a non-invasive cosmetic processing on the skin by creating multiple focal points with an individual transducer includes coupling a transducer module with an acoustic probe, wherein the ultrasonic probe comprises a first switch for control ultrasonic imaging, wherein the ultrasonic probe comprises a second switch to control acoustic therapy to cause a plurality of individual areas of cosmetic treatment, wherein the ultrasonic probe comprises a movement mechanism to provide desired spacing between individual areas of cosmetic treatment, bringing into contact the transducer module with the skin surface of the subject, activating the first switch on the ultrasonic probe to form an image acoustically, with the transducer module, a region below the skin surface, and activating the second switch on the acoustic probe to deal acoustically, with the module transducer, the region below the surface of the skin in a desired sequence of individual areas of cosmetic treatment that is controlled by the movement mechanism, wherein the transducer module comprises an individual, individual ultrasound transducer configured to apply ultrasonic therapy to the tissue in a plurality of locations at a focal depth.

[00030] According to several modalities, an aesthetic treatment system for creating multiple focal points in tissue with an ultrasound transducer includes a control device that operably controls an ultrasonic treatment function to provide an ultrasonic treatment, and a wand. hand-held configured to direct the ultrasonic treatment in a sequence of individual zones of thermal cosmetic treatment. The hand wand includes a transducer configured to apply ultrasonic therapy to tissue in a plurality of locations at a focal depth. According to several modalities, the use of an aesthetic treatment system is for the non-invasive cosmetic treatment of the skin.

[00031] According to several modalities, An aesthetic ultrasound treatment system for creating multiple focus points with an ultrasound transducer includes an ultrasonic probe comprising an ultrasound transducer configured to apply ultrasonic therapy to tissue in a plurality of locations at a local depth with at least one of the group consisting of polarization by amplitude modulation and phase variation and a control module coupled to the ultrasonic probe to control the transducer of ultrasound. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby a plurality of portions of the ultrasound transducer is configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy phase variation whereby a plurality of portions of the ultrasound transducer are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, where a first phase is different from a second phase. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby a plurality of portions of the ultrasound transducer are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude, and applying phase variation of ultrasonic therapy whereby a plurality of portions of the ultrasound transducer are configured to emit ultrasonic therapy to a plurality of phases of acoustic intensity, wherein a first phase is different from a second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the ultrasound transducer comprises the piezoelectric material and the plurality of portions of the ultrasound transducer are configured to create a plurality of corresponding variations of piezoelectric material in response to an electric field applied to the ultrasound transducer. In one embodiment, the plurality of variations of piezoelectric material comprise at least one of expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, at least a portion of the ultrasonic transducer is configured to emit ultrasonic therapy at two or more amplitudes of acoustic intensity, and where the amplitude of the ultrasonic therapy emitted by at least a portion of the piezoelectric material varies over time. . In several embodiments, the ultrasonic treatment is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a removal of tattoo, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation and an acne treatment.

[00032] According to several modalities, an aesthetic treatment system for use in cosmetic treatment to create multiple focal points with an ultrasound transducer includes an ultrasonic probe that includes a first switch that operably controls a function of forming a ultrasonic images to provide ultrasonic imaging, a second switch that operably controls a function of the ultrasonic treatment to provide an ultrasonic treatment, and a movement mechanism configured to direct the ultrasonic treatment at least one sequence of individual zones of cosmetic, thermal treatment. The system includes a transducer module configured to apply ultrasonic therapy with at least one of the group consisting of amplitude modulation polarization and phase variation, where the transducer module is configured both to form ultrasonic images and for ultrasonic treatment, where the Transducer module is configured for coupling to the ultrasonic zone, wherein the transducer module comprises an ultrasound transducer configured to apply ultrasonic therapy to the tissue in a plurality of locations at a focal depth, wherein the transducer module is configured to operably couple at least one of the first switch, second switch and the movement mechanism, and a control module, wherein the control module comprises a processor and a screen for controlling the transducer module. In one embodiment, the ultrasound module comprises an individual ultrasound transducer. In one embodiment, the ultrasound module comprises an individual ultrasound transduction element. In one embodiment, the ultrasound module comprises an individual ultrasound transducer comprising an individual transduction element. In one embodiment, the plurality of locations are placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second set of locations is placed within a second cosmetic treatment zone. The first zone that is different from the second zone. In one embodiment, the first cosmetic treatment zone comprises a substantially linear sequence of the first set of locations and the second cosmetic treatment zone comprises a substantially linear sequence of the second set of locations. In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude modulation whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from A second amplitude. In one embodiment, the transducer module is configured to apply ultrasonic therapy phase variation whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, wherein a first phase is different from A second phase In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude modulation whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude, and applying phase variation of ultrasonic therapy whereby a plurality of portions of the transducer module are configured to emit ultrasonic therapy to a plurality of phases of acoustic intensity, wherein a first phase is different from a second phase. In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the transducer module comprises piezoelectric material and the plurality of portions of the transducer module are configured to create a plurality of corresponding variations of piezoelectric material in response to an electric field applied to the transducer module. In one embodiment, the plurality of variations of piezoelectric material comprises at least one of material expansion and material contraction. In one embodiment, at least a portion of the transducer module is configured to allow ultrasonic therapy at two or more amplitudes of acoustic intensity, and where the amplitude of the ultrasonic therapy emitted by at least a portion of the transducer module varies over time. . In one embodiment, the movement mechanism is configured to be programmed to provide variable spacing between a plurality of individual zones of cosmetic, thermal treatment. In one embodiment, a sequence of individual cosmetic, thermal treatment zones has a treatment spacing in a range of about 0.01 mm to about 25 mm. In one embodiment, the first and second switches comprise keys or buttons operated by user. In one mode, at least one of the first switch and the second switch is activated by the control module. In one embodiment, the treatment function is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a tattoo removal, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation and acne treatment [00033] In one embodiment, an imaging system and cosmetic treatment for use in cosmetic treatment includes an ultrasonic probe configured for ultrasonic treatment and ultrasonic imaging of the tissue in a plurality of locations at a focal depth. In one embodiment, the probe includes a transducer module configured for coupling of the ultrasonic probe, wherein the transducer module comprises an ultrasound transducer configured to apply ultrasonic therapy to tissue in a plurality of locations at the focal depth. In one embodiment, a first switch that operably controls an ultrasonic imaging function to provide ultrasonic imaging. In one embodiment, a second switch that operably controls an ultrasonic treatment function to provide ultrasonic therapy. In one embodiment, a movement mechanism is configured to direct the ultrasonic treatment in at least one sequence of individual zones of cosmetic, thermal treatment, wherein the transducer module is configured to operably couple at least one of the first switch, the second switch and the movement mechanism. In one embodiment, the control module comprises a processor and a screen to control the transducer module. In one embodiment, the module is removable. For example, in some non-limiting modes the transducers are configured for a tissue depth of 1.5 mm, 3 mm, 4.5 mm, 6 mm, less than 3 mm, between 1.5 mm and 3 mm, between 1.5 mm and 4.5 mm, more 4.5 mm, more than 6 mm, and anywhere in the ranges of 0.1 mm-3 mm, 0.1 mm-4.5 mm, 0.1 mm-25 mm, 0.1 mm-100 mm, and any depth between them.

[00034] In several embodiments, the plurality of locations are placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second set of locations is placed within a second cosmetic treatment zone, the first zone that is different from the second zone. In one embodiment, the first cosmetic treatment zone comprises a substantially linear sequence of the first set of locations and the second cosmetic treatment zone comprises a substantially linear sequence of the second set of locations. In one embodiment, the transducer module is configured to apply ultrasonic therapy using amplitude modulation whereby the transducer module comprises a plurality of portions that are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the transducer module is configured to apply ultrasonic therapy phase shunt so the transducer module comprises a plurality of portions that are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, wherein a first phase It is different from a second phase.

[00035] In one embodiment, a movement mechanism is a movement mechanism. In several embodiments, a movement mechanism is configured to move a transducer within a module or a probe. In one embodiment, a transducer is supported by a transducer support. In one embodiment, the transducer support includes a sleeve that moves along motion restriction bearings, such as linear bearings, specifically, a bar (or shaft) to ensure repeated linear motion of the transducer. In one embodiment, the sleeve is a slot bushing that prevents rotation around a groove shaft, but any guide is appropriate to maintain the movement path.

[00036] In one embodiment, the transducer support is actuated by a movement mechanism, which can be located in a hand wand or in a module, or in a probe. In one embodiment, a movement mechanism 400 includes any or more than one or more of a stop yoke, a movement member, and a magnetic coupling. In one embodiment, the magnetic coupling helps move the transducer. A benefit of a movement mechanism is that it provides a more precious, accurate and efficient use of an ultrasound transducer, for purposes of therapy and / or imaging. An advantage that this type of movement mechanism has with respect to the fixed, conventional arrangements of multiple transducers fixed in place in a housing is that the fixed arrangements are fixed with a separation distance.

[00037] By placing the transducer on a track (for example, such as a linear track) under the control of the controller, the modalities of the system and device provide adaptability and flexibility, in addition to efficiency, accuracy and precision. Adjustments can be made in real time and almost in real time to the imaging and placement of the treatment along the movement controlled by the movement mechanism. In addition to the ability to select almost any resolution based on the increasing adjustments made possible by the movement mechanism, adjustments can be made if the imaging detects abnormalities or conditions that merit a change in target selection and treatment spacing. In one embodiment, one or more sensors can be included in the module. In one embodiment, one or more sensors can be included in the module to ensure that a mechanical coupling is actually coupled between the movement member and the transducer support. In one embodiment, an encoder can be placed on top of the transducer holder and a sensor can be placed in a portion of the module, or vice versa (exchanged).

[00038] In several embodiments the sensor is a magnetic sensor, such as a giant magnetoresistive effect (GMR) or Hall effect sensor, and the encoder can be a magnet, a collection of magnets, a multi-pole magnetic strip. The sensor can be placed as a starting position of the transducer module. In one embodiment, the sensor is a contact pressure sensor. In one embodiment, the sensor is a pressure sensor in contact on a surface of the device to perceive the position of the device or the transducer in the patient. In several embodiments, the sensor can be used to correlate the position of the device or a component in the device in one, two, or three dimensions. In one embodiment, the sensor is configured to perceive the position, angle of inclination, orientation, location, elevation, or other relationship between the device (or a component thereof) and the patient. In one embodiment, the sensor comprises an optical sensor. In one embodiment, the sensor comprises a roller ball sensor. In one embodiment, the sensor is configured to correlate a position in one, two and / or three dimensions to compute a distance between areas or lines of treatment on the skin or tissue in a patient.

[00039] The movement mechanism can be any movement mechanism that can be found that is useful for transducer movement. Other modalities of movement mechanisms useful herein may include worm gears and the like. In several embodiments, the movement mechanism is located in a module 200. In several embodiments, the movement mechanism can provide linear, rotational, multi-dimensional movement or action, and the movement can include any collection of points and / or orientations in space. Various movement modalities can be used according to the various modalities, including but not limited to rectilinear, circular, elliptical, arc, spiral, a collection of one or more points in space, or any other positional and attitudinal movement modality. 1-D, 2-D or 3-D. The speed of the movement mechanism can be set or can be controlled in an adjustable way by a user. In one embodiment, the speed of the movement mechanism for

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<td> [00040]</td><td>In</td><td colspan="2">various modalities,</td><td>the</td><td>module</td><td>transducer</td><td>I know</td>

configured to apply ultrasonic therapy using amplitude modulation whereby the transducer module comprises a plurality of portions that are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude, and applying phase derivation of ultrasonic therapy whereby the transducer module comprises a plurality of portions that are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, wherein a first phase is different from a second phase.

[00041] In one embodiment, the plurality of phases comprises discrete phase values. In one embodiment, the transducer module comprises piezoelectric material and the plurality of portions of the transducer module is configured to create a plurality of corresponding variations of piezoelectric material in response to an electric field applied to the transducer module. In one embodiment, the plurality of variations of piezoelectric material comprises at least one of material expansion and material contraction. In one embodiment, the transducer module comprises at least a portion that is configured to emit ultrasonic therapy at two or more amplitudes of acoustic intensity, and wherein the amplitude of ultrasonic therapy emitted by at least a portion of the transducer module varies with the pass of the time.

[00042] In one embodiment, the movement mechanism is configured to be programmed to provide variable spacing between a plurality of individual zones of cosmetic, thermal treatment. In one embodiment, a sequence of individual cosmetic, thermal treatment zones has a treatment spacing in a range of about 0.01 mm to about 25 mm (for example, 1 mm, 1.5 mm, 2 mm, 1-5 mm). In one embodiment, the first and second switches comprise keys or buttons operated per user. In one mode, at least one of the first switch and the second switch is activated by the control module.

[00043] In several modalities, the treatment function is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a treatment of sunburn, a tattoo removal, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation, and an acne treatment. In one embodiment, the transducer module is configured to provide an acoustic power of the ultrasonic therapy in a range of between about 1 W to about 100 W (for example, 5-40 W, 10-50 W, 25-35 W) and a frequency of about 1 MHz to about 10 MHz to heat the tissue thermally to cause coagulation. In one embodiment, the acoustic power may be from a range of 1 W to about 100 W in a frequency range of about 1 MHz to about 12 MHz (for example, 4 MHz, 7 MHz, 10 MHz, 4-lOMHz), or from about 10 W to about 50 W at a frequency range of about 3 MHz to about 8 MHz. In one embodiment, the power and acoustic frequencies are from about 40 W to about 4.3 MHz and about 30 W to about 7.5 MHz. An acoustic energy produced by this acoustic power can be between about 0.01 joules (J) at about 10 J or about 2 J to about 5 J. In one embodiment, the acoustic energy is in a range less than about 3 J.

[00044] In several embodiments, a multi-focal ultrasound treatment system includes a control device that operably controls an ultrasonic treatment function to provide an ultrasonic treatment and a hand wand configured to direct the ultrasonic treatment in a sequence. of individual areas of cosmetic, thermal treatment. The hand wand includes a transducer configured to apply ultrasonic therapy to the tissue at a location at a focal depth, the location placed within a cosmetic, thermal treatment zone, where the transducer is further configured to apply ultrasonic therapy to the tissue simultaneously in a plurality of locations at the focal depth.

[00045] In several embodiments, a multi-focal treatment and aesthetic imaging system includes an ultrasonic probe comprising an ultrasound transducer configured to apply ultrasonic therapy to tissue in a plurality of locations at a focal depth with at least one of the group consisting of phase shunt and amplitude modulation polarization and a control module coupled to the ultrasonic probe to control the ultrasound transducer. In one embodiment, the plurality of locations is placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second set of locations is placed within a second cosmetic treatment zone, the first zone that is different from the second zone. In one embodiment, the first cosmetic treatment zone comprises a substantially linear sequence of the first set of locations and the second cosmetic treatment zone comprises a substantially linear sequence of the second set of locations. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby the ultrasound transducer comprises a plurality of portions that are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein a first amplitude is different from a second amplitude. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy phase shunt so that the ultrasound transducer comprises a plurality of portions that are configured to emit ultrasonic therapy at a plurality of acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the ultrasound transducer is configured to apply ultrasonic therapy using amplitude modulation whereby the ultrasound transducer comprises a plurality of portions that are configured to emit ultrasonic therapy at a plurality of acoustic intensity amplitudes, wherein the first amplitude is different from a second amplitude, and applying phase derivation of ultrasonic therapy whereby the ultrasound transducer comprises a plurality of portions that are configured to emit ultrasonic therapy to a plurality of acoustic intensity phases, wherein a first phase is different from a second phase. In one embodiment, the plurality of phases comprises discrete phase values.

[00046] In one embodiment, the ultrasound transducer comprises piezoelectric material and the plurality of portions of the ultrasound transducer is configured to create a plurality of corresponding variations of piezoelectric material in response to an electric field applied to the ultrasound transducer. In one embodiment, the plurality of piezoelectric material variations comprise at least one of the expansion of the piezoelectric material and contraction of the piezoelectric material. In one embodiment, the ultrasonic transducer comprises at least a portion that is configured to emit ultrasonic therapy at two or more amplitudes of acoustic intensity, and wherein the amplitude of the ultrasonic therapy emitted by at least a portion of the piezoelectric material varies with the pass of the time. In one embodiment, the system also includes a movement mechanism configured to be programmed to provide variable spacing between the plurality of individual cosmetic treatment zones. In one embodiment, a sequence of individual cosmetic treatment zones has a treatment spacing in a range of about 0.01 mm to about 25 mm. In one embodiment, the ultrasonic treatment is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a removal of tattoo, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation, and an acne treatment. In one embodiment, the ultrasonic transducer is configured to provide an acoustic power of the ultrasonic therapy in a range of between about 1 W to about 100 W and a frequency of about 1 MHz to about 10 MHz to heat the tissue thermally to cause coagulation.

[00047] In several embodiments, a treatment system includes a control device that operably controls an ultrasonic treatment function to provide an ultrasonic treatment, and a hand wand configured to direct the ultrasonic treatment in a sequence of individual zones of thermal cosmetic treatment. In one embodiment, the hand wand includes a transducer configured to simultaneously apply the ultrasonic therapy to the tissue in a plurality of locations at a focal depth.

[00048] In several embodiments, a system for performing a cosmetic procedure that is not performed by a doctor, includes an ultrasonic probe comprising a transducer module. In one embodiment, the transducer module comprises an ultrasound transducer configured to apply ultrasonic therapy to tissue in a plurality of locations at a focal depth with at least one of the group consisting of phase shunt and amplitude modulation polarization. In one embodiment, the ultrasonic probe comprises a first switch to control acoustic imaging, the ultrasonic probe comprises a second switch to control acoustic therapy by causing a plurality of individual areas of cosmetic treatment, and the ultrasonic probe comprises a mechanism of movement to provide desired spacing between individual areas of cosmetic treatment.

[00049] In several embodiments, the aesthetic imaging and treatment system for use in cosmetic treatment includes an ultrasonic probe. In one embodiment, a transducer module includes an ultrasound transducer configured to apply ultrasonic therapy through an opening in an acoustically transparent member to form a thermal coagulation point (TCP) at a focal depth in the tissue. In one embodiment, a first switch operably controls an ultrasonic imaging function to provide ultrasonic imaging, a second switch operably controls an ultrasonic treatment function to provide ultrasonic treatment, and a mechanism is configured. movement to direct the ultrasonic treatment in at least one sequence of individual cosmetic, thermal treatment zones. In several embodiments, the transducer module is configured both to form ultrasonic images and for ultrasonic treatment, the transducer module is configured for coupling to the ultrasonic probe, the transducer module is configured to be operably coupled to at least one of the first switch, the second switch and the movement mechanism. In one embodiment, a control module comprises a processor and a screen to control the transducer module.

[00050] In one embodiment, the plurality of locations is placed in a substantially linear sequence within a cosmetic treatment zone. In one embodiment, a first set of locations is placed within a first cosmetic treatment zone and a second location zone is placed within a second cosmetic treatment zone, the first zone that is different from the second zone. In one embodiment, the first cosmetic treatment zone comprises a substantially linear sequence of the first set of locations and the second cosmetic treatment zone comprises a substantially linear sequence of the second set of locations. In one embodiment, the movement mechanism is configured to provide fixed spacing between a plurality of individual zones of cosmetic, thermal treatment. In one embodiment, a sequence of individual cosmetic, thermal treatment zones has a treatment spacing in a range of about 0.01 mm to about 25 mm. In one embodiment, the first and second switches comprise keys or buttons operated by user. In one embodiment, the treatment function is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a tattoo removal, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation, and an acne treatment. In one embodiment, the transducer module is configured to provide an acoustic power of the ultrasonic therapy in a range of between about 1 W to about 100 W and a frequency of about 1 MHz to about 10 MHz to heat the tissue thermally to cause coagulation.

[00051] In several embodiments, a cosmetic treatment system includes a control device that operably controls an ultrasonic treatment function to provide ultrasonic treatment at different depths below the surface of the skin, and a configured hand wand. to direct the ultrasonic treatment to two or more focal depths below the surface of the skin, the hand wand configured to connect at least two interchangeable transducer modules configured to apply the ultrasonic treatment to the two or more focal depths below the skin surface, where each of the transducer modules is configured to create one or more sequences of thermal coagulation points (TCP).

[00052] In one embodiment, the system also includes an image forming transducer configured to provide images at least one depth below the surface of the skin. In one embodiment, the system also includes a movement mechanism to place the sequence of individual discrete lesions in a linear sequence. In one embodiment, the transducer modules comprise at least one transducer module that is configured to provide ultrasound therapy in a range of between about 1 W to about 100 W and a frequency of about 1 MHz to about 10 MHz. In one mode, the Transducer modules comprise a transducer module that is configured to provide therapy at a depth of 3 mm. In one embodiment, the transducer modules comprise a transducer module that is configured to provide therapy at a depth of 4.5 mm.

[00053] In one embodiment, the at least two interchangeable transducer modules comprise a first interchangeable transducer module that is configured to treat a first focal depth below the skin surface with a first therapeutic transduction element, wherein the at least two interchangeable transducer modules comprise a second interchangeable transducer module that is configured to treat a second focal depth below the skin surface with a second therapeutic transduction element, wherein the hand wand is configured to connect to one of the first interchangeable transducer module and the second interchangeable transducer module in a moment, wherein the system further comprises a screen to show a first image of the first focal depth below the surface of the skin and a second image of the second focal depth below the surface of the skin.

[00054] In one embodiment, the hand wand is configured to connect to one of the at least two interchangeable transducer modules at a time, the at least two interchangeable transducer modules comprise a first module that is configured to treat a first focal depth below the skin surface with a first individual element of ultrasound therapy, and a second module that is configured to treat a second focal depth below the skin surface with a second individual element of ultrasound therapy. In one embodiment, the creation of the one or more thermal coagulation point sequences (TCP) comprises the creation of multiple linear sequences of thermal coagulation points (TCP).

[00055] In one embodiment, an image forming transducer is configured to provide images of at least one depth below the surface of the skin, where the individual areas of cosmetic, thermal treatment are individual discrete lesions, and further comprising a movement mechanism to place the sequence of individual discrete lesions in a linear sequence, wherein the transducer modules comprise at least one transducer module that is configured to provide ultrasound therapy in a range of between about 1 W to about 100 W and a frequency of about 1 MHz to about 10 MHz, wherein the transducer modules comprise a transducer module that is configured to provide therapy at a depth of 3 mm or 4.5 mm, and wherein the treatment function is at least one of a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a removal of tattoo, a skin stretch, a vein removal, a vein reduction, a sweat gland treatment, a hyperhidrosis treatment, a sunspot removal, a fat treatment, a vaginal rejuvenation, and an acne treatment.

[00056] In several of the modalities described herein, the procedure is completely cosmetic and not a medical act. For example, in one embodiment, the methods described herein need not be performed by a doctor, but in a spa institute or other aesthetic institute. In some embodiments, a system for non-invasive cosmetic skin treatment can be used.

[00057] The methods summarized above and set forth in detail further below describe certain actions taken by a practitioner; however, it should be understood that they may also include the instruction of these actions by a third party. Thus, actions such as coupling a transducer module with an ultrasonic probe include instructing the coupling of a transducer module with an ultrasonic probe.

[00058] Additionally, the areas of applicability will become apparent from the description provided herein. It should be noted that the description and specific examples are proposed for illustration purposes only and are not intended to limit the scope of the modalities described herein.

Brief Description of the Figures [00059] The figures described herein are for illustration purposes only and are not intended to limit the scope of the present description in any way. The modalities of the present invention will become more fully understood from the detailed description and the attached figures where:

[00060] Figure 1 is a schematic illustration of an ultrasound system according to various embodiments of the present invention.

[00061] Figure 2 is a schematic illustration of an ultrasound system coupled to a region of interest according to various embodiments of the present invention.

[00062] Figure 3 is a schematic partial sectional illustration of a portion of a transducer according to various embodiments of the present invention.

[00063] Figure 4 is a partial sectional side view of an ultrasound system according to various embodiments of the present invention.

[00064] Figures 5A-5D are graphs illustrating the time delays to reach a focal point for several transducers according to various embodiments of the present invention.

[00065] Figures 6A-6C are graphs illustrating phase delays to reach a focal point for several transducers according to various embodiments of the present invention.

[00066] Figures 7A-7C are graphs illustrating quantified phase delays to reach a focal point for several transducers according to various embodiments of the present invention.

[00067] Figures 8A-8B are graphs illustrating profiles of quantified phase delays to reach a focal point for several transducers according to embodiments of the present invention.

[00068] Figure 9 is a schematic illustration of the characteristics of the polarized piezoelectric material according to an embodiment of the present invention.

[00069] Figures 10A-10B are graphs illustrating approximations of amplitude modulation according to various embodiments of the present invention.

[00070] Figures 11A-11H are schematic and graphic illustrations illustrating modulation functions and corresponding intensity distributions according to various embodiments of the present invention.

[00071] Figures 12A-12D are graphs illustrating modulation functions and corresponding intensity distributions according to various embodiments of the present invention.

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[00075] Figures 16A-16B are graphs illustrating the performance of discrete phases in various approaches according to various embodiments of the present invention.

[00076] Figures 17A-17D are schematic illustrations of hybrid and graphic systems illustrating their performance according to various embodiments of the present invention.

[00077] Figure 18 is a schematic illustration of a two-phase changeable system according to an embodiment of the present invention.

[00078] Figures 19A-19C are graphs of an intensity distribution before focusing according to an embodiment of the present invention.

[00079] Figures 20A-20C are graphs of an intensity distribution in the approach according to an embodiment of the present invention.

[00080] Figure 21 is a schematic illustration of an amplitude modulation aperture pattern according to an embodiment of the present invention.

[00081] Figures 22A-22C are graphs of an intensity distribution of an amplitude modulated aperture before focusing according to an embodiment of the present invention.

[00082] Figures 23A-23C are graphs of an intensity distribution of an amplitude modulated aperture in focus according to an embodiment of the present invention.

[00083] Figure 24 is a schematic illustration of an amplitude modulated aperture pattern with changing states according to an embodiment of the present invention.

[00084] Figures 25A-25D are graphs of an intensity distribution of an amplitude modulated aperture with changing states prior to focusing according to an embodiment of the present invention.

[00085] Figures 26A-26C are graphs of an intensity distribution of an amplitude modulated aperture with changing states in focus according to an embodiment of the present invention.

[00086] Figure 27A is a schematic illustration of an amplitude modulated aperture with two levels of change according to an embodiment of the present invention.

[00087] Figure 27B is a state transition table of the schematic view of Figure 27A according to an embodiment of the present invention.

[00088] Figure 28A is a schematic illustration of an amplitude modulated aperture with three levels of change according to an embodiment of the present invention.

[00089] Figure 28B is a state transition table of the schematic view of Figure 28A according to an embodiment of the present invention.

[00090] Figure 29A is a schematic illustration of an amplitude modulated aperture with four levels of change according to an embodiment of the present invention.

[00091] Figure 29B is a state transition table of the schematic view of Figure 29A according to an embodiment of the present invention.

Detailed Description of the Invention [00092] The following description sets forth examples of modalities, and is not intended to limit the present invention or its teachings, applications or uses thereof. It should be understood that throughout the figures, corresponding reference numbers indicate similar or corresponding parts and characteristics. The description of the specific examples indicated in the various embodiments of the present invention is intended for purposes of illustration only and is not intended to limit the scope of the invention described herein. In addition, the citation of multiple modalities that have the indicated characteristics is not proposed to exclude other modalities that have additional characteristics, or other modalities that incorporate different combinations of the indicated characteristics. Additionally, features in one modality (such as in a figure) can be combined with descriptions (and figures) of other modalities.

[00093] In various embodiments, the systems and methods for ultrasound treatment of tissue are configured to provide cosmetic treatment. In several modalities, the tissue below or even on the surface of the skin such as the epidermis, dermis, fascia, muscle, fat and superficial muscular aponeurotic system (SMAS), are treated non-invasively with ultrasound energy. The ultrasound energy can be focused on one or more treatment points, may not be focused and / or unfocused, and may be applied to a region of interest that contains at least one epidermis, dermis, hypodermis, fascia, muscle, fat and SMAS to achieve a cosmetic and / or therapeutic effect. In various modalities, the systems and / or methods provide non-invasive dermatological treatment to tissue through heat treatment, coagulation, ablation, and / or stretching. In several embodiments described herein, non-invasive ultrasound is used to achieve one or more of the following effects: a facial lift or rejuvenation, an eyebrow lift, a chin lift, an eye treatment, a wrinkle reduction, a scar reduction, a burn treatment, a tattoo removal, a vein removal, a vein reduction , a treatment on a sweat gland, a hyperhidrosis treatment, sun spot removal, an acne treatment, and a pimple removal. In one embodiment, fat reduction is achieved. In one embodiment, the neckline is treated. In some modalities, two, three or more beneficial effects are achieved during the same treatment session, and it can be achieved simultaneously. In another embodiment, the device can be used in adipose tissue (for example, fat). In another embodiment, the system, device and / or method may be applied to the genital area (for example, a vaginal rejuvenation vagina and / or vaginal narrowing, such as to narrow the supportive tissue of the vagina).

[00094] Several embodiments of the present invention relate to devices or methods for controlling the distribution of energy to the tissue. In various embodiments, various forms of energy may include acoustic, ultrasonic, light, laser, radiofrequency (RF), microwave, electromagnetic, radiation, thermal, cryogenic, electron beam, photon-based, magnetic, magnetic resonance, and / or energy Other forms of energy. The various embodiments of the present invention relate to devices or methods for dividing a beam of ultrasonic energy into multiple beams. In various embodiments, devices or methods can be used to alter the distribution of ultrasound acoustic energy in any of the procedures such as, but not limited to, therapeutic ultrasound, diagnostic ultrasound, non-destructive testing (NDT) using ultrasound, ultrasonic welding, any application that includes the coupling of mechanical waves to an object, and other procedures. In general, with therapeutic ultrasound, a tissue effect is achieved by concentrating acoustic energy using focusing techniques from the opening. In some cases, high intensity focused ultrasound (HIFU) is used for therapeutic purposes in this way. In one embodiment, a tissue effect created by the application of therapeutic ultrasound at a given depth can be referred to as the creation of a thermal coagulation point (TCP). It is through the creation of PCT in particular positions that thermal and / or mechanical tissue ablation can occur non-invasively or remotely.

[00095] In one embodiment, TCP can be created in a linear or substantially linear sequence or zone, with each individual TCP separated from its neighboring TCPs by a treatment spacing. In one embodiment, multiple TCP sequences can be created in a treatment region. For example, PCTs can be formed along a first linear sequence and a second linear sequence separated by a treatment distance from the first linear sequence. Although treatment with therapeutic ultrasound can be administered through the creation of individual PCTs in a sequence and sequences of individual PCTs, it may be desirable to reduce the treatment time and the corresponding risk of pain and / or discomfort experienced by a patient. The therapy time can be reduced by forming multiple PCTs simultaneously, almost simultaneously, or sequentially. In some modalities, treatment time can be reduced 10%, 20%, 25%, 30%, 35%, 40%, 4%, 50%, 55%, 60%, 65%, 70%, 75%, 80% or more when creating multiple TCP.

[00096] Several embodiments of the present invention face potential challenges presented by the administration of ultrasound therapy. In several embodiments, the time to effect the formation of TCP for a desired cosmetic and / or therapeutic treatment for a desired clinical approach in a target tissue is reduced. In several modalities, the target tissue, but is not limited to, any of the skin, eyelids, eyelashes, eyebrows, lacrimalis caruncle, crow's feet, wrinkles, eye, nose, mouth, tongue, teeth, gums, ears, brain, heart, lungs, ribs, abdomen, stomach, liver, kidneys, uterus, breast, vagina, prostate, testicles, glands, thyroid glands, internal organs, hair, muscles, bones, ligaments, cartilage, fat, labuli fat, adipose tissue, subcutaneous tissue, implanted tissue, an implanted organ, lymphoid, a tumor, a cyst, an abscess, or a portion of a nerve, or any combination of this.

[00097] In some embodiments, discrete fastening and / or amplitude modulation techniques can be applied to an aperture configured to emit ultrasonic energy. This can cause the division of an ultrasonic beam emitted by the opening into multiple beams, which can distribute simultaneously, substantially simultaneously, or sequentially ultrasonic energy to multiple locations or focal points. In some embodiments, amplitude modulation can be combined with techniques configured to change the modulation states of an opening in order to reduce the intensity of the ultrasonic energy distributed to tissues located before and / or after the focal points. In several modalities, the therapy time can be reduced by 1-24%, 1-26%, 1-39%, 1-50%, or more than 50%.

[00098] Various modalities of imaging devices and ultrasound treatment are described in the

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<td>which is a</td><td>Phase</td><td>National US according</td><td> 35</td><td>OR</td><td>. SC</td><td> . § 371</td><td>of the</td>

International Application No. PCT / US2009 / 046475, filed on June 5, 2009 and published in English on December 10, 2009, claiming the priority benefit of Provisional US No. 61 / 059,477 filed on June 6, 2008 , each of which is incorporated in its entirety as a reference herein.

System overview [00099] With reference to the illustration in Figure 1, one mode of an ultrasound system 20 includes a hand wand 100, module 200 and a controller 300. Hand wand 100 can be coupled to controller 300 by an interface 130, which can be a wired or wireless interface. The interface 130 can be coupled to the hand wand 100 by a connector 145. The remote end of the interface 130 can be connected to a controller connector in a circuit 345. In one embodiment, the interface 130 can transmit controllable power from the controller 300 to the hand wand 100.

[000100] In various embodiments, the controller 300 can be configured for operation with the hand wand 100 and the module 200, as well as the functionality of the complete ultrasound system 20. In several modes, multiple controllers 300, 300 ', 300, etc. can be configured. for operation with multiple hand wands 100, 100 ', 100, etc. and / or multiple modules 200, 200 ', 200, etc. The controller 100 may include an interactive graphic display 310, which may include a touch monitor and a graphic user interface (GUI) that allows the user to interact with the ultrasound system 20. As illustrated, the graphic display 315 includes an interface touch 315. In several modalities, the screen 310 establishes and presents the operating conditions, including the activation status of the equipment, treatment parameters, messages and system messages, and ultrasound images. In various embodiments, the controller 300 can be configured to include, for example, a microprocessor with software and input / output devices, systems and devices for controlling electronics and / or mechanical scanning and / or transducer multiplexing and / or multiplexing of transducer modules, a system for the distribution of energy or power, systems for monitoring, systems to perceive the spatial opposition of the probe and / or transducers and / or multiplexing of transducer modules, and / or systems to handle user input and record treatment results, among others. In various embodiments, the controller 300 may include a system processor and various analog and / or digital control logic, such as one or more of microcontrollers, microprocessors, field programmable gate arrangements, computer cards, and associated components, including firmware or control software, which may be able to interconnect user controls and interconnection circuits as well as input / output circuits and systems for communications, displays, interconnection, storage, documentation and other useful functions. The system software that runs in the system process can be configured to control all the initialization, synchronization, level adjustment, monitoring, safety monitoring and all other functions of the ultrasound system functions to achieve the treatment objectives defined by the user. Additionally, the controller 300 may include several input / output modules, as well as switches, buttons, etc., which can also be configured appropriately to control the operation of the ultrasound system 20.

[000101] As illustrated in Figure 1, in one embodiment, controller 30 may include one or more data ports 390. In various embodiments, data ports 390 may be a USB port, Bluetooth port, IrDA port, port parallel, serial port and the like. Data ports 390 may be located on the front, side and / or back of controller 300, and may be used to access storage devices, printing devices, computing devices, etc. The ultrasound system 20 may include a lock 395. In one embodiment, in order to operate the ultrasound system 20, the lock 395 must be unlocked so that a power switch 393 can be activated. In one embodiment, the secure 395 can be connected to the controller 300 via a data port 390 (for example, a USB port). The lock 395 can be unlocked by inserting into the data port 390 an access key (for example, USB access key), a hardware key, or the like. The controller 300 may include an emergency stop button 392, which can be easily accessible for emergency deactivation.

[000102] In one embodiment, the hand wand 100 includes one or more finger-activated switches or controllers, such as 150 and 160. In one embodiment, the hand wand 100 may include a removable module 200. In other embodiments, the Module 200 may be non-removable. The module 200 can be mechanically coupled to the hand wand 100 using a latch or coupler 140. An interface guide 235 can be used to assist the coupling of the module 200 for hand wand 100. The module 200 may include one or more ultrasound transducers. In some embodiments, an ultrasound transducer includes one or more ultrasound elements. The module 200 may include one or more ultrasound elements. The hand wand 100 may include image forming modules only, treatment only modules, image forming and treatment modules and the like. In one embodiment, the control module 300 can be coupled to the hand wand 100 via the interface 130, and the graphical user interface 310 can be configured to control the module 200. In one embodiment, the control module 300 can provide energy to hand wand 100. In one embodiment, hand wand 100 may include a source of energy. In one embodiment, switch 150 can be configured to control a tissue imaging function and switch 160 can be configured to control a tissue treatment function.

[000103] In one embodiment, module 200 can be coupled to hand wand 100. Module 200 can emit and receive energy, such as ultrasonic energy. The module 200 can be electronically coupled to the hand wand 100 and this coupling can include an interface that is in communication with the controller 300. In one embodiment, the interface guide 235 can be configured to provide electronic communication between the module 200 and the hand wand 100. The module 200 may comprise various probe and / or transducer configurations. For example, module 200 can be configured for a combined dual mode imaging / therapy transducer, coupled or co-housed image / therapy transducers, separate therapy and imaging probes, and the like. In one embodiment, when module 200 is inserted into or connected to the hand wand, the controller 300 automatically detects it and updates the interactive graphic display 310.

[000104] In several modalities, the tissue below even on the surface of the skin such as the epidermis, dermis, hypodermis, facia and superficial muscular aponeurotic system (SMAS), and / or muscle are treated non-invasively with energy from ultrasound. The tissue may also include blood vessels and / or nerves. The ultrasound energy can be focused, not focused or blur and apply a region of interest that contains at least one of the epidermis, dermis, hypodermis, facia and SMAS to achieve a therapeutic effect. Figure 2 is a schematic illustration of the ultrasound system 20 coupled in the region of interest 10. In various embodiments, the tissue layers of the region of interest 10 may be somewhere in the body of a subject. In one embodiment, the layers of tissue are in the head and region of the subject's face. The cross-sectional portion of the tissue of the region of interest 10 includes a skin surface 501, an epidermal layer 502, a dermal layer 503, a fat layer 505, a superficial muscular aponeurotic system 507 (hereinafter SMAS 507), and a 509 muscle layer. The tissue may also include hypodermis 504, which may include any tissue below the dermal layer 503. The combination of these layers in total can be known as subcutaneous tissue 510. Also illustrated in Figure 2 is a treatment zone 525 that it is below the surface 501. In one embodiment, the surface 501 may be a skin surface of a subject 500. Although a modality directed to therapy to a tissue layer can be used herein as an example, the system can be applied to any tissue in the body. In several modalities, the system and / or method can be used on muscles (or other tissue) of the face, neck, head, arms, legs or any other location in the body.

[000105] With reference to the illustration in Figure 2, one mode of the ultrasound system 20 includes hand wand 100, module 200, and controller 300. In one mode, module 200 includes a transducer 280. Figure 3 illustrates an embodiment of an ultrasound system 20 with a transducer 280 configured to treat tissue at a focal depth 278. In one embodiment, the focal depth 278 is a distance between transducer 280 and the target tissue for treatment. In one embodiment, a focal depth 278 is set for a given transducer 280. In one embodiment, a focal depth 278 is variable for a given transducer 280.

[000106] With reference to the illustration in Figure 4, the module 200 may include a transducer 280 that can emit energy through an acoustically transparent member 280. In several embodiments, a depth may refer to focal depth 278. In a mode, transducer 280 may have a deflected distance 270, which is the distance between transducer 280 and an acoustically transparent member surface 230. In one embodiment, the focal depth 278 of a transducer 280 is a fixed distance from the transducer. In one embodiment, a transducer 280 may have a fixed offset distance 270 from the transducer to the acoustically transparent member 280. In one embodiment, an acoustically transparent member 280 is configured in a position in module 200 or the ultrasound system 20 to make contact with the skin surface 501. In several embodiments, focal depth 278 exceeds the deflected distance 270 by an amount that corresponds to treatment at a target area located at a tissue depth 279 below the skin surface 501. In several embodiments, when the ultrasound system 20 placed in physical contact with the skin surface 501, the tissue depth 279 is a distance between the acoustically transparent member 230 and the target area, measured as the distance from the wand portion handheld 100 or module surface 200 that makes contact with the skin (with or without an acoustic coupling gel, medium, etc.) and the depth in the tissue from the point of contact on the skin surface to the target area. In one embodiment, the focal depth 278 may correspond to the sum of a deflected distance 270 (as measured by the surface of the acoustically transparent member 230 in contact with a coupling means and / or skin 501) in addition to a tissue depth 279 under the surface of the skin 501 to the target or target region. In several embodiments, acoustically transparent member 230 is not used.

[000107] The coupling components may comprise various substances, materials and / or devices to facilitate the coupling of transducer 280 or module 200 to a region of interest. For example, the coupling components may comprise an acoustic coupling system configured to acoustically couple the ultrasound signals and energy. The acoustic coupling system with possible connections such as a collector can be used to couple the sound in the region of interest, to provide lens focusing filled with liquid or fluid. The coupling system can facilitate this coupling through the use of one or more coupling means, including gases, water, liquids, fluids, gels, solids, non-gels, and / or any combination thereof, or any other means that allows that the signals are transmitted between transducer 280 and a region of interest. In one embodiment, one or more coupling means is provided within a transducer. In one embodiment, a fluid-filled module 200 contains one or more coupling means within a housing. In one embodiment, a fluid filling module 200 contains one or more coupling means within a sealed housing, which is separable from a dry portion of an ultrasound device. In various embodiments, a coupling means is used to transmit ultrasound energy between one or more devices and the tissue with a transmission efficiency of 100%, 99% or more, 98% or more, 95% or more, 90% or more, 80% or more, 75% or more, 60% or more, 50% or more, 40% or more, 30% or more, 25% or more, 20% or more, 10% or more, and / or 5% or more.

[000108] In several embodiments, transducer 280 may image and treat a region of interest at any suitable tissue depth 279. In one embodiment, transducer module 280 may provide acoustic power or power in a range of approximately 1W or less, between about 1W or about 100W and more than about 100W. In one embodiment, transducer module 280 can provide acoustic power at a frequency of about 1 MHz or less, between about 1 MHz to about 10 MHz, and more than about 10 MHz. In one mode, module 200 has a focal depth 278 for a treatment at a tissue depth 279 of approximately 4.5 mm below the skin surface 501. Some non-limiting modes of transducers 280 or modules 200 can be configured to distribute ultrasonic energy at a tissue depth of 3 mm, 4.5 mm, 6 mm, or less than 3 mm, between 3 mm and 4.5 mm, between 4.5 mm and 6 mm, more than 4.5 mm, more than 4 mm, etc., and anywhere in the ranges of 0-3 mm, 0.4.5 mm, 0-6 mm, 0-25 mm, 0-100 mm, etc., and any depth in this. 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 to a first tissue depth (for example, approximately 4.5 mm) and a second transducer module can apply treatment to a second tissue depth (for example approximately 3 mm), and a third Transducer module can apply treatment to a third tissue depth (for example approximately 1.5-2mm). In one embodiment, at least some or all of the transducer modules can be configured to apply treatment at substantially equal depths.

[000109] In several embodiments, changing the number of focus point locations (such as with a tissue depth 279) for an ultrasonic procedure can be advantageous because it allows the treatment of a patient at varying tissue depths. even if the focal depth 278 of a transducer 270 is set. This can provide synergistic results and maximize the clinical results of an individual treatment session. For example, treatment at multiple depths under an individual surface region allows a greater total volume of tissue treatment, resulting in improved collagen formation and narrowing. Additionally, treatment at different depths affects different types of tissue, thus producing different clinical effects that together provide a total, improved cosmetic result. For example, surface treatment can reduce the visibility of wrinkles and deeper treatment can induce the formation of more collagen growth. Similarly, treatment in several locations at the same or different depth may improve a treatment.

[000110] Although the treatment of a subject in different locations in one session may be advantageous in some modalities, sequential treatment over time may be beneficial in other modalities. For example, a subject can be treated under the same surface region at a depth once, at a second depth in a second time, etc. In several modalities, the time may be in the order of nanoseconds, microseconds, milliseconds, seconds, minutes, hours, days, weeks, months, or other periods of time. The new collagen produced by the first treatment may be more sensitive to subsequent treatments, which may be desired for some indications. Alternatively, treatment at multiple depths under the same surface region in a single session may be advantageous because treatment at one depth can synergistically improve or complement treatment at another depth (due to, for example, blood flow enhanced, growth factor stimulation, hormonal stimulation, etc.). In several modalities, different transducer modules provide treatment at different depths. In one embodiment, an individual transducer module can be adjusted or controlled for varying depths. Safety features can be used to minimize an incorrect depth being selected, in conjunction with the individual module system.

[000111] In several embodiments, a method of treating an area of the neck or lower face (for example, the submental area) is provided. In several embodiments, a method is provided for treating (for example, softening) the mentholabial folds. In other embodiments, a method of treating the eye region is provided. An improvement in the laxity of the upper eyelid and periorbital lines will be achieved and the texture improved by several modalities when treating at varying depths. By treating in varied locations in an individual treatment session, optimal clinical effects (for example, softening, stretching) can be achieved. In several embodiments, the treatment methods described herein are non-invasive cosmetic processes. In some embodiments, the methods can be used in conjunction with invasive processing such as liposuction or surgical face lifts, where skin tightening is desired. In several modalities, the methods can be applied to any part of the body.

[000112] In one embodiment, a transducer module allows a sequence of treatment at a fixed depth at or below the surface of the skin. In one embodiment, a transducer module allows a treatment sequence at a fixed depth below the dermal layer. In several embodiments, the transducer module comprises a movement mechanism configured to direct the ultrasonic treatment in a sequence of individual thermal lesions (hereinafter thermal coagulation points or TCP) at a fixed focal depth. In one embodiment, the linear sequence of individual TSP has a treatment spacing in a range of about 0.01 mm to about 25 mm. For example, the spacing may be 1.1 mm or less, 1.5 mm or less, between approximately 1.1 mm and approximately 1.5 mm, etc. In one mode, individual TCPs are discrete. In one mode, individual TCPs are overlapping. In one embodiment, the movement mechanism is configured to be programmed to provide variable spacing between individual TCPs. In several embodiments, the transducer module comprises a motion mechanism configured to direct the ultrasonic treatment in a sequence such that TCP is formed in linear or substantially linear sequences separated by a treatment distance. For example, a transducer module can be configured to form TCP along a first linear sequence and a second linear sequence separated by a treatment distance of the first linear sequence. In one embodiment, the treatment distance between adjacent linear sequences of the individual TCPs is in a range of about 0.01 mm to about 25 mm. For example, the treatment distance can be 2 mm or less, 3 mm or less, between about 2 mm and about 3 mm, etc. In several embodiments, a transducer module may comprise one or more motion mechanisms configured to direct the ultrasonic treatment in a sequence such that TCP is formed in linear or substantially linear sequences of individual thermal lesions separated by a treatment distance from other linear sequences. . In one mode,

<td>distance</td><td>from</td><td colspan="2">treatment</td><td>That separates</td><td colspan="2">the sequences</td>

<td colspan="3">linear or substantially</td><td colspan="2">TCP linear</td><td>it's the same</td><td>or</td>

<td>substantially</td><td>the</td><td>same.</td><td colspan="2">In one mode,</td><td>distance</td><td>from</td>

<td colspan="2">treatment that</td><td>To stop</td><td>the</td><td>sequences</td><td>linear</td><td>or</td>

<td>substantially</td><td></td><td>linear</td><td>from</td><td>TCP is</td><td>different</td><td>or</td>

<td>substantially</td><td colspan="2">different</td><td>for</td><td>several pairs</td><td>adjacent</td><td>from</td>

TCP linear sequences.

[000113] In one embodiment, first and second removable transducer modules are provided. In one embodiment, each of the first and second transducer modules is configured for both ultrasonic treatment and ultrasonic imaging. In one embodiment, a transducer module is configured for treatment only. In one embodiment, an image forming transducer can be attached to a probe handle or a hand wand. The first and second transducer modules are configured for interchangeable coupling to a hand wand. The first transducer module is configured to apply ultrasonic therapy to a first layer of tissue, while the second transducer module is configured to apply ultrasonic therapy to a second layer of tissue. The second layer of tissue is at a different depth than the first layer of tissue.

[000114] As illustrated in Figure 3, in various embodiments, the distribution of the emitted energy 50 at a suitable focal depth 278, distribution, synchronization and energy level are provided by the module 200 through the operation controlled by the control system 300 to achieve the desired therapeutic effect of controlled thermal injury to treat at least one of the epidermis layer 502, dermis layer 503, fat layer 504, SMAS layer 507, muscle layer 509 and / or hypodermis 504. Figure 3 illustrates a modality of a depth corresponding to a depth for treating muscle. In several modalities, the depth can correspond to any tissue, tissue layer, skin, epidermis, dermis, hypodermis, fat, SMAS, muscle, blood vessel, nerve or other tissue. During operation, module 200 and / or transducer 280 can also be scanned mechanically and / or electronically along surface 501 to treat an extended area. Before, during and after the distribution of the ultrasound energy 50 to at least one of the epidermis layer 502, dermis layer 503, and hypodermis 504, fat layer 505, the SHAS layer 507 and / or the layer of muscle 509, monitoring of the treatment area and surrounding structures can be provided to plan and assess the results and / or provide feedback to the controller 300 and the user via a graphical interface 510.

[000115] In one embodiment, the ultrasound system 20 generates ultrasound energy that is directed to and focused below the surface 501. This controlled and focused ultrasound energy 50 creates the thermal coagulation zone (TCP) 550. In One embodiment, the ultrasound energy 50 creates a gap in the subcutaneous tissue 510. In various embodiments, the emitted energy 50 has the target or target of the tissue below the surface 501 that cuts, ablates, coagulates, micro-ablates, manipulates and / or causes an injury 550 in the tissue portion 10 by below surface 501 at a specified focal depth 278. In one embodiment, during the treatment sequence, the transducer 280 moves in a direction denoted by the arrow marked 290 at specified intervals 295 to create a series of treatment zones 254 each of which receives an emitted energy 50 to create one or more TCP 550.

[000116] In several embodiments, the transducer modules comprise one or more transduction elements. The transduction elements may comprise a piezoelectrically active material, such as lead zirconate titanate (PZT), or any other piezoelectrically active material, such as a ceramic, crystalline, plastic and / or piezoelectric compound, as well as lithium niobate, Lead titanate, barium titanate and / or lead methaiobato. In various embodiments, in addition to, or instead, a piezoelectrically active material, the transducer modules may comprise any other material configured to generate radiation and / or acoustic energy. In several modalities, transducer modules can be configured to operate at different frequencies and treatment depths. The transducer properties can be defined by an outside diameter (OD) and focal length (EL). In one mode, a transducer can be configured to have OD = 19 mm and EL = 15 mm. In other embodiments, other suitable OD and EL values may be used, such as OD of less than about 19 mm, greater than about 19 mm, etc. and EL less than about 15 mm, greater than about 15 mm, etc. Transducer modules can be configured to apply ultrasonic energy at different depths of target tissue. As described above, in several embodiments, the transducer modules comprise motion mechanisms configured to direct the ultrasonic treatment in a linear or substantially linear sequence of individual TCPs with a treatment spacing between the individual TCPs. For example, the treatment spacing can be approximately 1.1 mm, 1.5 mm, etc. In several embodiments, the transducer modules may further comprise motion mechanisms configured to direct the ultrasonic treatment in a sequence so that the TCPs are formed into separate linear or substantially linear sequences with a treatment spacing. For example, a transducer module can be configured to form TCP along a first linear sequence and a second linear sequence separated by the treatment spacing between about 2 mm and 3 mm from the first linear sequence. In one embodiment, a user can manually move the transducer modules across the surface of a treatment area so that adjacent linear sequences of TCP are created. In one embodiment, a movement mechanism can automatically improve the transducer modules across the surface of a treatment area so that adjacent linear sequences of TCP are created.

[000117] In several embodiments, the treatment can be advantageously distributed at a faster rate and with improved accuracy. This in turn can reduce the treatment time and decrease the pain experienced by the subject. Additionally, efficiency can be increased if the variation in treatment spacing between linear or substantially linear sequences of TCP is reduced. In one embodiment, a system uses a transducer configured to produce an individual focus treatment point. In one embodiment, the transducer can be mechanically moved along a line to create a linear sequence of TCP. For example, Table 1 provides an estimate of the time to create a linear sequence of TCP and an estimate of time to move between the linear sequences of TCP according to one modality. It can be seen that the time to create a linear sequence of TCP and the time to move between linear sequences of TCP are almost equivalent.

Table 1

<td>Time metric</td><td>Time (in msec)</td><td>Percentage of total time</td>

<td>Time to create a linear sequence</td><td> 2.9</td><td> 48</td>

<td>Time to move between linear sequences</td><td> 3.2</td><td> 52</td>

<td>Total time</td><td> 6.1</td><td> 100</td>

[000118] In several embodiments, therapeutic treatment can be advantageously distributed at a faster rate and with improved accuracy by using a transducer configured to distribute multiple focus points or TCP. This in turn can reduce the treatment time and decrease the pain experienced by the subject. In several embodiments, the treatment time is reduced if the time to create a linear TCP sequence and the time to move between the linear TCP sequences are reduced by issuing TCP in multiple locations from an individual transducer.

Therapy distribution using amplitude modulation Fourier transform and open spatial frequency analysis [000119] In various modalities, spatial frequency analysis techniques based on Fourier analysis and Fourier optics can be used to increase the efficiency of therapeutic treatment . When a system that has an impulse response h (t) is excited by a stimulus x (t), the relationship between the input x (t) and the output y (t) is related by the convolution function as follows:

y (t) = r (t) «h (t) = f ^ x (T} h (t - τ) άτ [000120] In transformed equations several modalities, Fourier can be applied to compute the convolution of the

The continuous one-dimensional Fourier transform can be defined as:

r (f - J'CrW = J and (t) ^ '' dt [000121] Here, f is the frequency, t is the time. It can be shown that the convolution in the time domain is equivalent to the multiplication in the frequency domain:

F (x (t) * h (t)) = = Y (f) (3 [000122] In several embodiments, the Fraunhofer approximation can be used to derive a relationship between a transducer opening or opening and a response resulting from the ultrasonic beam

The derivation of the Fraunhofer approach is described in Joseph Goodman, Introduction to Fourier Optics (3d ed. 2004), which is incorporated herein by reference in its entirety. According to the Fraunhofer approach, a pattern of complex far-field amplitude produced by a complex aperture is equal to a two-dimensional Fourier transform of the phase and aperture amplitude. In several modalities, this relationship in optics can be extended to ultrasound since linear wave equations can be used to represent both the propagation of light and the propagation of sound. In the case of optics and / or ultrasound, the two-dimensional Fourier transform can be determined from the distribution of sound wave pressure amplitude in the focus of a transducer.

[000123] In several embodiments, a HuygensFresnel integral determines a pressure amplitude U (Po) of an opening by integrating the effect (both amplitude and phase) of each resonator or transducer on a surface Σ. It can be expressed as:

U (POR)=&

faPa'Pl) = --COs (n (4b) [000124] where k is a wave number expressed as 2π / λ, roi is the distance from an opening to the screen in a field, n is a directional vector from the opening, U (Pi) is the pressure field at the opening, and U (P0) is the pressure field on the screen.

[000125] In several embodiments, the following assumption is used to lead to an approximation that the amplitude in the pressure field U (Po) is a two-dimensional Fourier transform of UIPi). First, at small angles, the cosine function of the angle between n and is 1. This leads to the following exemplifications:

* 01> 1) [000126] where z represents the depth. Second, the Fresnel approach of distanceroi, can be expressed, using a binomial expansion, such as:

[000127] Third, it can be assumed that the observation plane is much larger than the dimensions of the aperture as follows:

[000128] If these assumptions apply to equations (4a) and (4b), then the amplitude in the field can be expressed as:

[000129] Equation (5) includes a quadratic phase term outside the integral that does not affect the total magnitude. Comparing equation (5) to equation (2) reveals a similarity in the arguments within the integral. In particular, instead of a dimensional function and (t) evaluated at sequences f, a two-dimensional function U (xl, yl) is evaluated at spatial frequencies given as:

(5a) (5b) [000130] Because the integral of equation (5) is the two-dimensional Fourier transform, equation (5) can be rewritten as:

[000131] In several modalities, the phase and amplitude functions at the opening U (xl, yl) can be separated into two functions, specifically a function of xl and a function of yl, respectively.

u (xItem y ±) = ^ (^ ι) Λ (μ) (7) [000132] Applying equation (7) to equation (6) leads to further simplification:

[000133] Equation (8) demonstrates that a response of the aperture in the field for a separable two-dimensional function is the multiplication of two one-dimensional Fourier transforms in the xl and yl directions. Additionally it can be shown that equations (6) and (8) are maintained for a focused system with the exception that the spatial frequency arguments change as expressed in equations (9a) and (9b). For a focused system, the variable z that represents the depth can be replaced with z £ that represents a focal length.

f _ χΰ / x ~ (9a) í - 3¾ (9b) [000134] In several modalities, Fourier transform identities and Fourier optics (some of which are listed in Table 2, below) can be used for ultrasound transducers in order of determining the intensity distribution that corresponds to a transducer design. For example, the Fourier transform of a rectangle (rect (ax) is a sinc function. As another example, the Fourier transform of a two-dimensional circle of uniform amplitude is a first-order Bessel function that can be represented as Ji.

Table 2

<td></td><td>Opening function</td><td>Transformed of Fourier</td>

<td>5 (pair of transformed two-dimensional)</td><td>circQ-s / x2 + y2)</td><td>+ Í} ·) VCS +% and</td>

[000135] In several embodiments, an ultrasound transducer can have a rectangular aperture of suitable dimensions and adequate focal length. In several embodiments, an ultrasound transducer can have a circular aperture with adequate dimensions and adequate focal length. In one embodiment, a transducer can have a circular opening with an outside radius of approximately

9.5 mm, an inner diameter of approximately 2 mm, and focal length of approximately 15 mm. The opening of a circular transducer can be described as:

f (x, y) = circ Q - circ (10a) r = y / x2 + y2 (10b) [000136] For example, a may be approximately 9.5 mm and b may be approximately 2 mm. By applying the Fourier transform (10a) an estimate of the sound wave pressure distribution in the approach can be provided.

f = (11) [000137] where y are the same as fx and fy of equations (9a) and (9b). Equation (11) demonstrates that the sound wave pressure distribution of a transducer with a circular aperture is a first-order Bessel function. In one embodiment, a substantial majority of the energy is concentrated in the focus (for example 15 mm away from the aperture). The width of a main ultrasonic beam and the distribution of energy away from the main beam is20 they can express as a function of the operating frequency as represented in equations (9a) and (9b).

[000138] In several modalities, two identical or almost identical beams can be created in the approach if the aperture was modulated (for example multiplied) by a correct function. In one embodiment, a cosine function can be applied to a circular opening as follows:

$ Cx, y) = cos (cx) and circ circ [000139] An energy distribution or beam response in the modulated aperture approach of equation (12) is the convolution of the Fourier transform of the two aperture functions:

(13) [000140] Equation (13) can be simplified by adding two separate functions by applying the Fourier transform identity for a Dirac delta function (for example, identity 2 in Table 2):

(14) [000141] Equation (14) shows that two beams that appear in the focus are spatially separated by ± compared to the original unmodulated beam. In several embodiments, one or more other modulation functions, such as sine function, can be used to achieve a desired beam response. In several modalities, the opening can be modulated so that more than two approaches are created. For example, three, four, five, etc., approaches can be created. In several embodiments, the aperture can be modulated such that the approaches are created sequentially or substantially sequentially instead of simultaneously.

[000142] In several embodiments, the therapy transducer modules comprise motion mechanisms configured to direct the ultrasonic treatment in a linear or substantially linear sequence of individual TCPs with a treatment spacing between the individual TCPs. For example, the treatment spacing can be approximately 1.1 mm,

1.5 mm, etc. In several embodiments, the transducer modules may further comprise motion mechanisms configured to direct the ultrasonic treatment in a sequence such that TCP is formed in linear or substantially linear sequences separated by a treatment spacing. For example, a transducer module can be configured to form TCP along a first linear sequence and a second linear sequence separated by treatment spacing between approximately 2 mm and 3 mm from the first linear sequence. According to equation (14), a simultaneous or substantially simultaneous separation in the ultrasonic beam in the focus (or before the focus) can be achieved if the aperture is modulated by a cosine and / or sine function of a desired spatial frequency. In one embodiment, two beams simultaneously or almost simultaneously focused, separated by a treatment spacing of approximately 1.1 mm can be created in a linear or substantially linear sequence. At an ultrasound frequency of 7 MHz, the wavelength χ of the ultrasound wave in water is approximately 0.220 mm. Therefore, the spatial frequencies ξχ and in the approach they are represented as:

(15a) (15b) [000143] In order to place two approaches separated by approximately 1.1 mm, then the spatial frequency to modulate the opening is calculated as follows. Using entities 3 and 4 in Table 2, the Fourier transformation of a sine or cosine function is a Dirac delta function with the argument:

χη fe-, arg = —--- (16a)

3.3 [000144] In one mode, equation (16a) can be solved for Kx when the argument is 0:

2icrand

(16b) [000145] Additionally, Xq can be replaced by half of the separation distance (for example, 1.1 mm):

S „1.1

2τγ— ¡at— = = = <16th>

[000146] In several embodiments, a circular opening transducer that emits ultrasonic energy at various operating frequencies can be modulated by sine and / or cosine functions for the spatial frequencies listed in Table 3. The modulated opening of the transducer can produce a beam. simultaneously or substantially simultaneously divided with two approaches that have different separation distances, as indicated in Table 3. In one embodiment, the transducer can have OD of approximately 19 mm and a focal length of approximately 15 mm.

Table 3

<td></td><td colspan="4">Distance of separation between approaches</td>

<td>Frequency ultrasound</td><td>1.1 mm</td><td>1.5 mm</td><td>2 mm</td><td>3 mm</td>

[000147] As shown in Table 3, in several embodiments, a spatial frequency of an aperture modulation function increases as the ultrasonic operating frequency for a given distance of focus separation increases. In addition, the spatial frequency increases as the desired distance of focus separation increases.

[000148] In one embodiment, the higher spatial frequency may result in transitions of amplitude in the aperture that occurs more rapidly. Due to the processing limitations of the transducer, the rapid variations in amplitude in the opening can make the opening less efficient since there may be a variation in the amount of sound pressure produced by the different parts of the opening. In one embodiment, using spatial frequencies to simultaneously or almost simultaneously divide the beam can reduce the full focal gain of each beam. As shown in equation (14), a field pressure in the focus of each beam is reduced by a factor of two compared to an unmodulated beam. In one embodiment, the sound pressure or ultrasound intensity of the aperture can be increased to obtain similar or substantially similar intensities in the focal plane. However, in one embodiment, the increase in opening pressure cannot be limited by the processing limitations of the transducer and / or system. In one embodiment, an increase in the opening pressure can increase the total intensity in the near field, which may increase the possibility of excessive heating of the tissue of the treatment area that is located before focusing. In one embodiment, the possibility of additional pre-focal tissue heating can be limited or eliminated by using a lower frequency of ultrasound treatment.

[000149] In one embodiment, the application of the aperture modulation function as shown in equation (12) results in two simultaneous or substantially simultaneous ultrasound beams in the focus. In several embodiments, the ultrasound beam can be divided multiple times, such as three, four, five, and so on. sometimes, such that multiple simultaneous or almost simultaneous beams are created. In one embodiment, four equally separate beams can be generated along one dimension by modulating or multiplying the opening by two separate spatial frequencies:

g (x, y) ~ (cos (cx) + cos (dx)) (circ - circ (|)) + to'ty)+ “To '+ +to '(17b) [000150] As shown in equation (17b), the unmodulated focus beam can be created in four different locations along the x-axis. In one embodiment, a constant or term DC, Cl, can be added to the amplitude modulation function to maintain the placement of energy in the original focal location:

g (x, y) = (cos (cx) + cos (dx) + Ct) circ Q) - circ (^ (18a) (18b) [000151] In one mode, the modulation aperture of equations (17) and (18), so the beam can be located in multiple locations simultaneously or almost simultaneously , may have limited applicability due to system, material and / or tissue limitations. In one embodiment, due to the possibility of heating the tissues of the treatment area located before the focus, the frequency of ultrasound therapy can be adjusted, such as decreasing, in order to limit and / or eliminate this possibility. In one embodiment, non-linear techniques can be applied in the approach in order to limit and / or eliminate the possibility of pre-focal tissue heating. In one embodiment, the sound pressure or ultrasound intensity from the opening can be increased to obtain similar or substantially similar intensities in the focal plane.

[000152] In several embodiments, as shown in equation (7), if the amplitude and phase functions in the aperture can be separated, the two-dimensional Fourier transform of a sound pressure function U (xi, yi) is It can be expressed as a product of a two-dimensional Fourier transform of two functions in x and y, shown in equation (8). In several embodiments, it can be advantageous to create multiple TCPs in a linear or substantially linear sequence, as well as create multiple linear sequences simultaneously or almost simultaneously. As shown in Table 1, in one mode, if two TCPs are created simultaneously or substantially simultaneously in a linear sequence, but linear sequences are created sequentially, the total treatment time can be reduced by approximately 24 %. In one embodiment, if four CTPs are created to handle simultaneously or substantially simultaneously in a linear sequence, but linear sequences are created sequentially, the total treatment time can be reduced by approximately 39%. In one embodiment, if two TCPs are created simultaneously or substantially simultaneously, together with two linear sequences, the total treatment time can be reduced by approximately 50%.

Division of multiple beams in two dimensions [000153] In several modalities, four TCPs can be created, such as two in each in two linear or substantially linear sequences, using the following aperture amplitude modulation function:

gQx, y) = cos (cx) cos (dy) I throw Í-) - pull [000154] The Fourier transform of this function is:

έ) +F (<«- £ l + - i A + £) + (19b) [000155] As shown in equations (19a) and (19b), the beam can be modulated in two linear sequences, with each sequence having two approaches. In one embodiment, the linear sequences can be orthogonal. In one embodiment, the linear sequences may not be orthogonal.

Because the Fourier transform is multiplied by i in equation (19b), the amplitude of the beam or intensity is reduced compared to the beam divided into two approaches (for example, as shown in equation (14)).

In one embodiment, due to the possibility of heating the tissues of the treatment area that are located before the focus, the frequency of ultrasound therapy can be adjusted, such as

100 decrease, in order to limit and / or eliminate the possibility of excessive heating of localized tissues before focusing. In several embodiments, modulation can be applied so that linear or substantially linear sequences of TCP are created sequentially or substantially.

[000156] In several modalities, as shown in equations (12) to (14), the amplitude modulation by cosine and / or sine through a transducer having a linear aperture creates two separate beams derived by a spatial frequency of the cosine and / or sine modulation function. In several modalities, the modulation function can be varied in phase or spatially as follows:

= cos (cx - &) (circ (j) tire (20a) [000157] In one modality, the amplitude caused by the derivation is the same as that in equation (14). In one modality, although the spatial derivation ( for example, the angle Θ) does not change the total amplitude in the approach, the phase is modified. In several ways, the modification

101 of the phase can be advantageous to reduce a peak intensity before focusing. In several embodiments, an aperture can be designed so that the pre-focal or near-field heating of the tissue is substantially minimized while substantially increasing the focus intensity or focal gain.

Therapy distribution using phase shunt [000158] In several modalities, the beam can be divided axially. It may be advantageous to analyze this axial division through an analysis of time delays and the application of discrete fascination. In several embodiments, the beam division axially in the xy / od direction can be combined with planar or dimensional amplitude modulation of the aperture (for example, such as those shown in equations (19a) and (19b)), which can result in the division of the beam into two or three dimensions. In

<td colspan="2">various modalities, the beam</td><td>I know</td><td>can divide</td><td>when using</td><td>the</td>

<td>inclination of</td><td>phase in</td><td>the</td><td>opening, which</td><td>may</td><td>be</td>

<td>substantially</td><td>equivalent</td><td>to</td><td>the derivation</td><td>space.</td><td>In</td>

Several modalities, the phase inclination can be performed using the following Fourier transform pair:

= + j sen (ax) (21 s)

102

(21b) [000159] In one embodiment, this function describes an opening that is only modulated in phase since the magnitude of the exponential term is one. In one embodiment, each spatial location has an element that is under a different phase that can be expressed as the ratio of the imaginary (sine) and real (cosine) parts as follows:

==; tan “(22) [000160] Equation (22) spatially expresses the phase differences.

[000161] In several embodiments, the time delays associated with the propagation of ultrasound waves can be used to describe the shunt or phase inclination for the focus of the beam. In one embodiment, a transducer opening may be a focused circular bowl that has the following geometry:

<td> [000162]</td><td>The</td><td>equations (23a)</td><td>Y</td><td>(23b)</td><td>describe a bowl</td>

<td>circular</td><td>what</td><td>is focused on</td><td>the</td><td>apex</td><td>of the bowl with a</td>

focal length zf. In one mode, the approach can be

103 move from (0, 0, zf) to a spatial point P0 that is

<td>Located in</td><td>(χο,</td><td>yO, zO).</td><td>Distance to</td><td>this new</td><td>point</td>

<td>P0 space</td><td>since</td><td colspan="2">any point in the</td><td>bowl it</td><td>may</td>

<td>express as</td><td></td><td></td><td></td><td></td><td></td>

[000163] where (xl, yl, zl) are points in the bowl opening that are defined by equations (23a) and (23b). In one embodiment, in order to determine the real time at the target or target P0, then the speed of sound c (343.2 m / s) can be divided into a propagation distance d as follows:

(xi-arpF + Cyj -y9 ) (25) [000164] In one mode, in order to obtain a desired constructive interference associated with the propagation of delayed ultrasound waves in the focus, equation (25) can be used to calculate the relative time delay to another party of the opening. In one embodiment, this can be achieved by subtracting equation (25) for the minimum time delay. The remaining time is the additional time for the ultrasound waves emitted by other parts of the opening to arrive at the new point

104 PO space.

[000165] In several embodiments, a focus point of (0, 0, 15 mm) can be moved to a different focus point P0. Relative time delays to the new focus point PO relative to the center or apex of the opening bowl (as expressed in radial distance) can be calculated using equation (25) and are illustrated in Figures 5A-5D for a Gue transducer has geometry of outer diameter (OD) = 19 mm, inner diameter (ID) = 4 mm, and a distance to focus (FL) = 15 mm. Other modalities may use other dimensions, the present examples illustrate a non-limiting modality. Other dimensions are contemplated. Figure 5A illustrates the relative time delay 1002a (in microseconds) for the acoustic energy that travels from a spatial point in the aperture to reach an objective focus point P0 = (0, 0, 15 mm) relative to variable radial locations in the bowl opening according to one modality. As expected, the delay illustrated in Figure 5A is zero since the target target point is the same as the focal point and the focus point has not changed. Figure 5B illustrates the relative time delay 1002b (in microseconds) for the acoustic energy that travels from a spatial point in the aperture to reach a target or target focus point P0 = (0, 0, 10 mm) in relation to variable radial locations at the opening of

105 Bowl according to a modality. As illustrated, the radial position starts at 2 mm due to a hole in the center of the transducer bowl. In one embodiment, an image forming element can be placed in the hole. The time to the target or target point PO = (0, 0, 10 mm) increases as the radial position in the bowl increases. Figure 5C illustrates the relative delay of time 1002c (in microseconds) for the acoustic energy that travels from a spatial point in the aperture to reach a target or target point P0 = (0, 0, 20 mm) relative to variable radial locations in the opening of the bowl according to a modality. As illustrated, if the focus is changed to P0 = (0, 0, 20) mm, the time to the target or target decreases as the radial position in the bowl increases. Figure 5D illustrates the relative delay of time 1002d (in microseconds) for acoustic or sound energy traveling from a spatial point in the aperture to reach an objective or target focus point PO = (2 mm, 0, 14.7 mm ) in relation to variable radial locations in the opening of the bowl according to one modality. In one embodiment, the total distance from the vertex to the target or target point P0 = (2 mm, 0.14.7 mm) is approximately 15 mm. As illustrated, if the focus is derived at P0 = (2 mm, 0, 14.7 mm), the time to the target or target is linearly dependent on the x coordinate of the position in the bowl. The

106

<td>Time to</td><td>the</td><td>Diana is</td><td>minor for</td><td>positions</td><td>what</td><td>they have x</td>

<td>positive</td><td>to the</td><td>apex and</td><td>older for</td><td>positions</td><td>what</td><td>they have x</td>

<td>negative</td><td>with</td><td>relationship</td><td>at the apex.</td><td colspan="2">Positions</td><td>what's wrong with it</td>

x coordinates between approximately 2 mm and approximately 2 mm are presented outside the inside diameter of the bowl (for example, where an imaging element may be located).

[000166] Figures 5A-5D illustrate time delays for the propagation of sound from several points in the aperture to constructively place the sound energy in the approach according to various modalities. A negative time in relation to zero implies that it takes less time for energy from that point to reach a new focus point. A positive time in relation to zero implies that it takes more time for energy to reach a new focus point. In one embodiment, if appropriate time delays can be placed at individual points of the bowl, time delays can be controlled to obtain constructive interference in the new approach. In one embodiment, for transducers comprising piezoelectrically active material, the movement of the approach from a mechanical approach (0, 0, zF) to a new focus point PO can change the distances that resonators must travel in the aperture (due to the expansion and / or contraction of the material) to create constructive interference in the focus

107

Ρ0. These distances can be converted to time delays by dividing the distances by the speed of sound. In one embodiment, if time delays for resonators on the opening surface are known, additional time delays to achieve the P0 approach can be taken into account so that the desired intensity of pressure in the PO approach can be achieved.

[000167] In several embodiments, the ultrasound wave of a variable frequency can be directed to a target or target area. In one embodiment, a transducer comprising piezoelectrically active material can be electrically excited by a continuous wave signal of a suitable operational frequency to achieve a suitable therapy frequency. In various modes of transducers, the operational frequency may be approximately 4 MHz, approximately 7 MHz, approximately 10 MHz, less than approximately 4 MHz (for example, between approximately 20 KHz and approximately 4 MHz), between approximately 4 MHz and approximately 7 MHz, greater than about 10 MHz, etc. In one embodiment, the continuous wave signal may be on or active for a period of between about 20 msec to 30 msec. This in turn may imply that the aperture is excited for between approximately 80,000 cycles to approximately 300,000 cycles of the excitation signal. In one mode, you can

108 using other suitable periods of the excitation signal that are active, such as, for example, less than about 20 msec, greater than about 30 msec, and the like. In one embodiment, a short duration of the excitation signal that is active may be unnecessary to obtain constructive interference in the focus. This may be the result of time delays for the propagation of an ultrasonic wave for different points of the aperture at a focus point P0 that is greater than the duration of the excitation signal that is active. In one embodiment, it may be sufficient to modify the phases corresponding to the opening locations based on the operational frequency without controlling the time delays to obtain constructive interference. In one embodiment, the phases corresponding to the aperture locations can be modified and, in addition, time delays can be controlled to obtain constructive interference at a new focus point.

[000168] Figures 6A-6C illustrate phase delays associated with the propagation of sound to the approach relative to the apex of an aperture according to various modalities. In one embodiment, phase delays are associated with time delays. Figure 6A illustrates the relative phase delays 1012a, 1014A and 1016A (in degrees) for sonar energy traveling from a space point in the

109 aperture to reach a target or target focus point PO = (0, 0, 10 mm) relative to variable radial locations in the bowl opening according to one modality. Curve 1012a corresponds to an excitation signal of approximately 4 MHz, curve 1014A corresponds to an excitation signal of approximately 7 MHz, and curve 1016a corresponds to an excitation signal of approximately 10 MHz. Figure 6B illustrates the relative phase delays 1012b, 1014b, and 1016b (in degrees) for sonar energy traveling from a spatial point in the aperture to reach a focus point or target P0 = (0, 0, 20 mm) in relation to variable radial locations in the opening of the bowl according to one modality. Curve 1012b corresponds to an excitation signal of approximately 4 MHz, curve 1014b corresponds to an excitation signal of approximately 7 MHz, and curve 1016b corresponds to an excitation signal of approximately 10 MHz. Figure 6C illustrates the relative phase delays 1012c, 1014c, and 1016c (in degrees) for sound energy traveling from a spatial point in the aperture to reach an objective or target focus point P0 = (2 mm, 0, 14 , 7 mm) in relation to variable radial locations in the opening of the bowl according to one modality. Curve 1012c corresponds to an excitation signal of approximately 4 MHz, curve 1014c corresponds to an excitation signal of approximately 7 MHz

110

MHz, and the 1016c curve corresponds to an excitation signal of approximately 10 MHz. As illustrated in Figures 6A6C, in one mode, if the aperture attempts to focus shallow, laterally deep, which can be related to the operational frequency , is related to a number of discontinuities in the phase delay. The number of discontinuities over a given length increases with the operational frequency of the excitation signal. In one embodiment, as explained below, manufacturing and system limitations may increase the number of discontinuities. In one embodiment, as illustrated in Figure 6B, the proportion of phase delay transitions is increased towards the edge of the transducer (for example, right part of the graph), regardless of whether the transducer is used to focus deep or little deep. In one embodiment, as illustrated in Figure 6C, the proportion of phase delay transitions is substantially constant when a transducer is used to tilt the beam. Figures 5B-5D and Figures 6A-6C illustrate additional time and phase to a focus point from a point in a transducer bowl. In one embodiment, the additional time and / or phase can be reduced or eliminated by placing an opposite of the time and / or phase delay in appropriate transducer locations. Therapy distribution using discrete phase shunt [000169] In one embodiment, the quantification of the phase and / or

111

<td>delay</td><td>can affect</td><td>the</td><td>precision to be</td><td>uses</td><td>for</td>

<td colspan="2">represent delays</td><td>from</td><td>Time and / or phase.</td><td>In</td><td>other</td>

<td>words,</td><td>It can be used</td><td>the</td><td>discrete delay and / or</td><td>the</td><td>phase</td>

discreet In one embodiment, an accuracy of time and / or phase delays can be limited by system parameters, such as the system clock and / or the number of bits available to represent the delay. In one embodiment, other system parameters may instead change the accuracy or additionally. In one embodiment, phase delays are also separated around the unit circle (360 °). In one embodiment, phase delays can be aperiodic or unevenly separated around the unit circle. Table 4 shows the levels of phase quantification according to various modalities. Additional numbers of levels (greater than 8) can be used in various modalities. As shown in table 4 two phases (N = 2), 0or and 180 °, it can represent a minimum level of phase control to change the focus point of an ultrasound beam according to one modality.

Table 4

<td>Number of levels (N)</td><td>Phases (degrees)</td>

112

[000170] Figures 7A-7C illustrate discrete or quantified phase delays for various levels of quantification, where phase delays are associated with the propagation of sound to the approach relative to the apex of an aperture according to various modalities. Figures 7A-7C illustrate the propagation of sound at an operational frequency of approximately 7 MHz. Figure 7A illustrates the relative, quantified phase 1022a, 1024a and 1026a (in degrees) phase delays for sonar energy that travels from a spatial point in the aperture to reach an objective or target focus point PO = (0, 0, 10 mm) in relation to variable radial locations in the opening of the bowl according to one modality. Curve 1022a corresponds to two levels of phase quantification, curve 1024a corresponds to three levels of phase quantification, and curve 1026a corresponds to four levels of phase quantification. Figure 7B illustrates the quantified, relative phase delays 1022b, 1024b, and 1026b (in degrees) for sound energy traveling from a spatial point in the aperture to reach an objective focus point PO = (0, 0, 20 mm) in relation to variable radial locations in the opening

113 of the bowl according to one modality. Curve 1022b corresponds to two levels of phase quantification, curve 1024b corresponds to three levels of phase quantification, and curve 1026b corresponds to four levels of phase quantification. Figure 7C illustrates the relative quantified phase delays 1022c, 1024c, and 1026c (in degrees) for sound energy traveling from a spatial point in the aperture to reach an objective focus point P0 = (2 mm, 0, 14.7 mm) in relation to radial variable locations in the opening of the bowl according to one modality. Curve 1022c corresponds to two levels of phase quantification, curve 1024c corresponds to three levels of phase quantification, and curve 1026c corresponds to four levels of phase quantification. In several modalities, as the number of quantification levels increases as shown in Figures 7A-7C (for example, curves 1026a, 1026b, and 1026c), the quantized phase delay patterns in a mode with a frequency of 7 MHz they become substantially similar to the non-quantified phase delay patterns shown in Figures 6A-6C (for example, curves 1014A, 1014b, and 1014c).

[000171] In an embodiment with reference to curve 1022c of Figure 7C (two-level phase quantification), it demonstrates that when a focused beam is directed 2 mm and -2 mm, a resulting phase delay pattern is substantially

114 similar with the transition from 0or at 180 ° which occurs at a substantially equal spatial frequency. There is a slight spatial derivation and phase delay pattern. Since the phase delay pattern is substantially similar to 2 mm and -2 mm, in one embodiment, the distribution of acoustic intensity in the focus may have a peak at both focus locations, simultaneously. In one embodiment, if the phase quantification is two levels, a phase solution for a specific approach will also be a solution for another location. In one embodiment, this result may be similar for the modification of the focus along the beam axis. If the phase quantification is two levels, then a solution for a flush can also be a solution for another approach.

[000172] Figure 8A illustrates discrete or quantified phase delays associated with sound propagation, at an operational frequency of approximately 7 MHz, for focus relative to the apex of an aperture according to various modalities. Figure 8A illustrates the relative phase delays 1032a and 1034a (in degrees) for sound energy traveling from a spatial point in the aperture to reach objective focus points (2 mm, 0, 14.7 mm) and (-2 mm, 0.14.7 mm) respectively. Curves 1032a and 1034a are shown in relation to variable radial locations in the bowl opening according to a

115 modality. In one embodiment, the level of quantification of the two is shown in Figure 8A. As shown in Figure 8A, the quantified phase delay patterns for the two approaches are substantially similar.

[000173] Figure 8B illustrates quantified or discrete phase delays associated with sound propagation, at an operational frequency of approximately 7 MHz, for focus relative to the apex of an aperture according to various modalities. Figure 8B illustrates the relative phase delays 1032b and 1034b (in degrees) for sound energy traveling from a spatial point in the aperture to reach objective focus points (0, 0, 10.25 mm) and (0, 0 , 27 mm), respectively. Curves 1032b and 1034b are shown in relation to variable radial locations in the bowl opening according to one modality. In one embodiment, the quantification level of the two is shown in Figure 8B. As shown in Figure 8B, the quantized phase delay patterns for the two approaches are substantially 180 ° out of phase.

[000174] In several embodiments, continuous or discrete amplitude modulation at an aperture and / or continuous or discrete phase delays can be used to focus an ultrasound beam. In one embodiment, it may be advantageous to provide a mechanical focal point instead of using the phase control and / or amplitude modulation of the aperture in

116 a flat aperture because the focal gain associated with the mechanical focus may be preferable. In one embodiment, the complexity of the system or opening design can be reduced, a mechanical approach can be created and phase delay and / or modulation techniques can be applied to the mechanical approach. An advantage may be a reduction in the number of discrete phase transitions to focus the beam on a new focal point. Another advantage may be that a distance between the different discrete phase levels can be increased when the aperture is already mechanically focused, which can result in the use of lower quantification levels, such as two, three, four, and so on.

[000175] In various embodiments, manufacturing methods can be used, including piezoelectric material polarization and / or discrete fastening of the system to manufacture transducers configured to divide or focus an ultrasound beam into two and / or three dimensions from a mechanical approach. The following lists several non-limiting examples of transducer designs. In various embodiments, other transducer designs can be manufactured using the methods described.

Multi-focal energy distribution using transducer polarization [000176] In several modes, a transducer can

117 understand piezoelectric material. The piezoelectric material can be polarized at elevated temperatures and high electric fields to create a net moment of dipole in the material. A net dipole moment may allow the piezoelectric material to have a piezoelectric effect that causes either a contraction or expansion of the material when an electric field is placed through all or part of the material in the direction of the dipole moment. In one embodiment, the parts of a transducer, such as a transduction element, can be treated to have different polarization moment characteristics. In one embodiment, an individual transduction element can be treated to have one, two, or more polarization characteristics. In one embodiment, an individual transduction element can be treated to have a pole. In another embodiment, parts of an element can be treated with one pole and the untreated parts of the element can have a second pole. In one embodiment, the polarization treatment can be painted on a transduction element.

[000177] Figure 9 shows a schematic diagram of a polarized piezoelectric material and the resulting behavior when a voltage is applied according to one mode. In one embodiment, a transducer can comprise the PZT 1052 piezoelectric material. The arrow shown in the PZT 1052 material is a net dipole moment. In a

118 mode, if a voltage is placed through the PZT 1052 material such that the electric field is in the opposite or substantially opposite direction of the dipole moment (as shown in 1082), then the material contracts. In one embodiment, if a voltage is placed through the PZT 1052 material such that the electric field is in the same or substantially the same direction as the dipole moment (as shown in 1072), then the material expands. In one embodiment, the PZT 1052 material does not expand or contract when no voltage is applied across the material, as shown in 1062.

[000178] In several embodiments, the polarization of the piezoelectric material can be used to implement the amplitude modulation of the aperture. In one embodiment, the two-level modulation can be equivalent to the two-level phase quantification. As shown in equations (12) - (14), an ultrasonic beam emitted by the opening of a transducer can be modulated to appear in two (or more) locations in a derived focal plane or changed by a distance that relates to the spatial frequency of a modulation function (for example, cosine and / or sine function). In one embodiment, the polarization direction can be used to modify the amplitude modulation by sine and / or cosine. As the picture shows. 9, in one mode, if the bias voltage or application to

119 Through all or part of the material you can provide three levels of amplitude modulation:

(material shrinkage), 1 (material expansion) and 0 (no change to the shape of the material). Figures 10A-10B illustrate approximations of amplitude modulation using two and three polarization levels according to various modalities. Figure 10A illustrates approximations of amplitude modulation using a sine function according to one modality. The x axis represents the relative distance with respect to an apex of the aperture and the Y axis represents the amplitude of the modulation function. Curve 1092A illustrates the modulation function (eg, sine function), curve 1094a illustrates the approximation using two polarization levels (for example, ± 1), and curve 1096a illustrates the approximation using three polarization levels (for example , + 1 and 0). Figure 10B illustrates approximations of amplitude modulation using a sine function with DC deviation of 0.25 according to one modality. The x-axis represents the relative distance with respect to an apex of the aperture and the y-axis represents the amplitude of the modulation function. Curve 1092B illustrates the modulation function (for example, sine function), curve 1094B illustrates the approximation using two polarization levels (for example, ± 1), and curve 1096b illustrates the approximation using three polarization levels (for example , ± 1 and 0). In one mode, such as

120 illustrated in Figure 10B, the width of a positive polarized region (having amplitude of 1) is greater than the width of a negative polarized region (having amplitude of -1) so that the average amplitude is substantially equal to the DC deviation (for example, 0.25). The limitation of two or three levels limits the C deviation achieved between -1 and 1. In several modalities more than three polarization levels can be used for amplitude modulation.

[000179] In one embodiment, in order to quantify the distribution of energy in the focus, then the square wave can be represented in terms of a function that has a related pair of Fourier transforms. The expansion of the Fourier series for a square wave of period c is:

+ ςββη (2ΐτ3ί *) + 7 sen (2w5ct) + ···) 'LZm-'X / IT x 3 ·> z (25) [000180] In one mode, a circular aperture with amplitude modulation described in the equation (25) can be described as:

opening (26a) [000181] The Fourier transform of this function is:

(26b)

121 [000182] Equation (26b) can be simplified as follows:

and «s (26c) [000183] In one embodiment, the sound wave pressure in the focal plane includes repetitive patterns of the main beam at multiple spatial locations separated by a distance 2c between each beam. Repetitive patterns may be decreasing in amplitude.

[000184] Figures 11A-11H illustrate some modalities of the apodization or aperture modulation functions (using two-level polarization or three-level polarization) and some corresponding normalized distributions of sound wave pressure intensity in the focus or approaches for a transducer excited by a 7 MHz excitation signal according to various modalities. In one embodiment, the transducers illustrated in Figures 11A-

<td colspan="2">11H are configured</td><td colspan="2">like bowls</td><td colspan="2">circular with</td><td>OD = 19 mm and</td><td>Fl</td>

<td>= 15 mm</td><td>The</td><td>figures</td><td>11 Α-</td><td>11B</td><td>illustrate</td><td>the profile</td><td>from</td>

<td>apodization</td><td>without</td><td>divide</td><td>εί</td><td>make</td><td>and one</td><td colspan="2">correspondent</td>

<td>distribution</td><td>from</td><td>intensity</td><td>from</td><td colspan="2">according to one</td><td>modality.</td><td>The</td>

Figure 11B illustrates that the intensity is concentrated in focus 1108. Figures 11C-11D illustrate the laterally split beam profile by approximately

122

1.1 mm between the focus peaks and a corresponding intensity distribution according to one modality. As illustrated by region 1104 in Figure 11A and region 1114 in Figure 11C, in several embodiments, part of an opening of the transducer has a zero apodization, which represents an inside diameter (ID) of the bowl. In some embodiments, these regions 1104 and 1114, which are illustrated as being approximately 4 mm in diameter, may correspond to regions where an image forming element can be located. In one embodiment, the apodization of the image forming element can be represented by region 1106.

[000185] With reference to Figure 11C, in one embodiment, the amplitude modulation for a 1.1 mm split between the focus peaks is illustrated. In one embodiment, if two levels of polarization or apodization are used, then 8 strips of substantially equal width (except at the edges) are defined on the opening surface. For example, two of these strips are marked 1112 and 1112 '. In one embodiment, the polarization of the strips alternates from -1 to +1 across the transducer surface. The resulting beam pattern is shown in Figure 11D. As expected, the ultrasonic beam appears in both approaches 1120 and 1120 'which is located at approximately -0.55 mm and 0.55 mm. The most frequent beam components are visible in regions 1122 and

123

1122 'at a distance of approximately 1.65 mm from the beam axis. In one embodiment, these components have less intensity than the focus regions 1120 and 1120 '. The higher frequency components may correspond to the third harmonic that has a lower intensity, as expressed in equation (26c). In various embodiments, as illustrated in Figures 11E-11H, the polarization of portions 1125, 1125 'of the transducer surface may include lines, curves, shapes, waves, patterns, and so on. In one embodiment, the characteristics of portions 1125, 1125 'can be used to maintain a focus division, and can redistribute energy pre-focally and / or postfocally for less heating.

[000186] In one embodiment, beam splitting can occur in both the x (azimuth) and y (elevation) dimensions. In one embodiment, divisions in the x and y axes can be treated independently when Fourier transform is performed. In one embodiment, an aperture can be designed to divide the beam in the x dimension by approximately 1.0 mm and in the y dimension by approximately 0.5 mm. The corresponding opening modulation function can be represented as:

^ Opening (x'you = (circleG) “circ

Θ) (27)

124 [000187] The spatial frequency for alternating amplitude modulation can be calculated as described above in conjunction with equations 26 (a) - (c), with the exception that the calculation is performed for two dimensions. Figures 12A12D illustrate some modalities of the apodization or aperture modulation functions (using two-level polarization) and a corresponding standardized intensity distribution of the sound wave pressure in the focus or approaches for a transducer excited by an excitation signal. 7 MHz according to several modalities. In one embodiment, the transducers illustrated in Figures 12A12D are configured as circular bowls with OD = 19 mm and FL = 15 mm Figure 12A shows an apodization function for opening according to one modality. As illustrated, the chessboard pattern 1132 and 1136 is alternating in amplitude in both the x and y directions. As illustrated in Figure 12B, the chessboard pattern produces four substantially different ultrasound beams 1140, 1140, 1142 'and 1142' separated by the expected distances, specifically, by approximately 1.0 mm in the xy direction and approximately 0.5 mm in direction and. In one embodiment, a five-point pattern can be achieved by adding a constant to the apex of the aperture, which can have a corresponding intensity distribution in the

125 origin.

[000188] In one embodiment, as illustrated in Figures 12C-12D, a line of four peaks is obtained by placing multiple frequencies along the same dimension (eg, dimension x). The modulation function can be (|) + (;)) (;) - ©) expressed as:

^ Opening _ C / cw <íra4o (28) [000189] Figure 12C shows an apodization function for opening according to one modality. As illustrated, pattern 1142 and 1146, for the polarization of the alternating strips from -1 to +1 across the transducer surface. As illustrated in Figure 12D, in one embodiment, the pattern produces four substantially different ultrasound beams 1150, 1152, 1154, and 1156 separated by approximately 1.0 mm and 3.0 mm in an x direction.

[000190] In one embodiment, an axial division of the beam or division along a dimension is achieved such that the beam remains symmetrical to the axis. In one embodiment, dividing the beam axially using two phases of polarization may be more difficult than obtaining a lateral direction. This may be due to the difficulty in obtaining the balance of intensity between the two or more peaks. In one mode, two phases can produce two peaks of simultaneous intensity

126 with one shallower than the other. The deepest intensity peak may be of less intensity than the shallowest peak due to the attenuation and additional diffraction in the tissue. In one embodiment, more than two phases can be used to achieve axial division.

[000191] In several embodiments, the division of an ultrasonic beam simultaneously, almost simultaneously, or sequentially at two or more focal points can be achieved through the application of discrete fascination of the system. Figure 13 is an illustration of a two phase system 1200 according to one embodiment. As illustrated, block 1202 is a source of AC voltage (or current) that drives discrete phase diverters, blocks 1204 and 1206 are discrete phase diverters by 0or and 180 °, respectively, and blocks 1208 and 1210 are transducer portions that are derived in phase. In one embodiment, discrete phase diverters 1204 and 1206 can be configured to derive the phase of the AC voltage (or current) signal supplied by source 1202, so that the resulting signals are 180 ° out of phase. In one embodiment, discrete phase diverters 1204 and 1206 can be configured to drive different portions of the transducer. In one embodiment, the 1200 system is configured to mimic two levels of polarization of the material. In one embodiment, it may be desirable to electrically isolate the transducer portions.

127

1208 and 1210. The corresponding connection and electrical isolation scheme can determine a beam pattern resulting in the approach according to one modality. In one mode, electrical isolation cannot be performed. With reference to Figure 1, in some embodiments, discrete phase diverters can be placed in or on the controller 300, hand wand 100, module 200, and / or transducers of the ultrasound system 20. In one embodiment, continuous phase shunt can be used.

[000192] In several embodiments, more than two discrete phase diverters can be used (for example, as shown in Table 4). The increase in the number of phases may result in an improved approximation of the phase delays for the direction and / or focus of the beam. In one embodiment, four discrete phase diverters can be used. Figure 14 is a schematic illustration of a selected, four-phase 1250 system according to one embodiment. As illustrated, blocks 1252, 1254, 1256, and 1258 are AC voltage (or current) sources that drive discrete phase diverters 1262, 1264, 1266, and 1268. Each discrete phase diverter block can be configured to provide four different phases 0or, 90 °, 180 ° and 270 °. In one embodiment, multiplexers 1272, 1274, 1276, and 1278 may be included to select a particular phase of a signal. The signal with the selected phase can be applied

128 to portions 1282, 1284, 1286, and 1288 of a 1280 transducer. In one embodiment, a portion is a part of an individual transducer with an individual transduction element. In one embodiment, a portion may be a transduction element. As illustrated, each portion 1282, 1284, 1286, and 1288 of transducer 1280 has a selectable phase (eg, 0 °, 90 °, 180 °, or 270 °). In one embodiment, portions 1282, 1284, 1286, and 1288 can be electrically isolated (for example, from one another). In one embodiment, if transducer 1280 is divided or segmented into portions 1282, 1284, 1286, and 1866, the ultrasonic beam can be operated and focused to multiple focus locations.

[000193] In one embodiment, an advantage of providing more discrete phase diverters can be illustrated by considering a ring or flat disk transducer and a measured intensity in focus compared to a measured intensity in the approach of a circular bowl transducer , focused substantially perfectly. Figure 15 illustrates the performance of a discrete phase system according to one modality. In one mode, the bowl transducer can be configured to have OD = 19 mm and FL = 15 mm, and its intensity (in dB) is illustrated by line 1302. The intensity of the flat ring transducer is illustrated by line 1306. As illustrated, the improvement in focal intensity

129 produced by the flat ring transducer increases (for example, exponentially) between approximately two and 5-6 discrete phase levels, but starts to level off after approximately 5-6 discrete phases. In one embodiment, the intensity is synthetically approaching approximately -2.3 dB (line 1304). As illustrated in one embodiment, the flat ring transducer (line 1306) produces a smaller focal gain than the bowl transducer (line 1302). As can be seen, in one embodiment, the addition of additional discrete phase levels can improve focus intensity and thereby improve transducer performance.

[000194] In one embodiment, a difference in intensity between a desired focus point and an ideal focus point can be changed by using a focused bowl. In one embodiment, a single bowl transducer with OD - 19 mm and 15 mm = Fl It can be used initially. Subsequently, in one embodiment, discrete fastening techniques can be used to move the focus to depth of approximately 12 mm or 18 mm. Figures 16A-16B are graphs illustrating the performance of discrete phase systems at various focus points according to various modalities. Figure 16A illustrates the performance 1316 of a bowl transducer (OD = 19 mm and FL = 15 mm) when the focus moves to 12 mm using discrete fascination compared to the 1312 performance of a

130 bowl transducer (OD = 19 mm bowl and Fl = 12 mm) according to one modality. As illustrated, line 1316 approaches asymptotically at approximately -1.3 dB (line 1314). In one embodiment, comparing line 1316 with the performance of the flat disk transducer, illustrated by line 1306 in Figure 15, the intensity produced by the bowl transducer has been improved. Figure 16B illustrates the performance 1326 of a bowl transducer (OD = 19 mm and FL = 15 mm) when the focus is moved to 18 mm using discrete fastening compared to the 1322 performance of a bowl transducer (OD = 19 mm bowl and FL = 18 mm) according to one modality. As illustrated, line 1326 approaches asymptotically at approximately 0.5 dB (line 1324). As illustrated, the performance of the bowl transducer with discrete fastening (line 1326) may exceed the performance of an ideal transducer (line 1322), such as when the number of discrete phase levels exceeds

<td>approximately</td><td>six.</td><td>In</td><td>a</td><td>modality,</td><td>can be</td>

<td>advantageous to use</td><td colspan="2">discrete phases</td><td>for</td><td>move the</td><td>focus more</td>

<td>Distribution of</td><td>therapy</td><td>using</td><td colspan="2">modulation of</td><td>amplitude and</td>

discrete phase shunt [000195] In various embodiments, amplitude modulation (for example, performed by polarization of material) can be used, in addition to discrete fastening. In one embodiment, the

131 Splitting an ultrasound beam can cause an increase in the power of the transducer that can be difficult to obtain due to, for example, the limitations of the transducer material or system. It may be desirable to phase-shift or phase-tilt the ultrasound beam from one focal position to another focal position. In one embodiment, the splitting of the ultrasound beam can be difficult to achieve due to the possibility of excessive heating of the tissue before focusing. In one embodiment, linear sequences of TCP can be created sequentially or substantially sequentially without moving a transducer, which can result in reduced therapy time. In one embodiment, the transducer can be moved to further distribute the treatment points. In one embodiment, a transducer can be a circular bowl transducer excited by the 7 MHz excitation signal and having 0D of approximately 19 mm, ID of approximately 4 mm, and FL of approximately 15 mm. Linear TCP sequences can be spaced by approximately 1.0 mm apart. It may be desirable to divide the ultrasound beam so that two linear TCP sequences are created simultaneously or substantially simultaneously by approximately 1.0 mm apart each. However, in one mode, compared to the intensity of a beam that is not divided, each

132 one of the divided beams can have an intensity that is approximately 2.4 times lower. Due to the potential for excessive heating of the tissue located before focusing, the power distributed to the transducer cannot be increased by approximately 2.4 times to compensate for the reduction in intensity. In one embodiment, quadrature fastening can be used to create linear TCP sequences one at a time. Quadrature fastening can be achieved by combining polarization of material with discrete fastening of the system. In one embodiment, the use of quadrature fastening may be related to an increase in power of approximately 1.2 times when quadrature fastening is applied to a focused bowl transducer. In one embodiment, this slight increase in power may be desirable.

[000196] Figures 17A-17B illustrate the quadrature control of a transducer by combining the polarization and discrete fastening of the system according to one modality. Figure 17A illustrates, in one embodiment, individual strips (for example, 1402, 1404, etc.) defined through a circular bowl transducer focused 1400 at a gap configured to achieve approximately 1.0 mm in the ultrasonic beam produced by the transducer. The focus of the transducer is an individual beam 1408 in the plane parallel to the face of the transducer. The 1400 transducer is not configured

133 With discreet fascination. In one embodiment, as illustrated in Figure 17B, the strips of the transducer 1410 are polarized by alternating the fastening direction. For example, strip 1412 has a phase of 0or and strip 1414 has a 180 ° phase. As shown in the intensity graph, two peaks of intensity 1418 and 1418 'appear substantially along a line at a focal depth.

[000197] In one embodiment, the creation of two peaks of intensity 1430 and 1432 may be undesirable due to system limitations (eg, power supply) and / or transducer materials. For example, more power may be needed to the transducer to create two TCPs simultaneously or almost simultaneously. Figure 17C illustrates the modulation of an opening of a transducer 1420 using an additional phase shunt (90 °) according to one embodiment. As illustrated, strip 1422 has a phase of 0or, and is further divided into a region or sub-strip 1426 that has a 90 ° phase and sub-strip 1428 that has a phase of 0or. Additionally, strip 1424 has a 180 ° phase (for example, alternating phase with respect to strip 1422), and is further divided into a region or sub-strip of 1430 having a 270 ° phase and sub-strip 1432 which has a 180 ° phase. In one embodiment, these two additional phases (for example, 1426 and 1428) can be electrically connected to transducer 1420 through a conductive joint and,

134 optionally a switch or flexible circuit configured to separate the two phases. Similar to the modalities illustrated in Figures 17A-17B, transducer 1420 is polarized so that the phase alternates between 0or and 180 ° between adjacent strips. In one embodiment, half of transducer 1420 is excited with a phase excitation signal of 0or and the other half is excited with a 180 ° phase excitation signal. In one embodiment, a separation of the phase variation is reduced by two with the additional fastening (for example, sub-strips 1426 and 1428). In one embodiment, when discrete fastening is combined with polarization (for example, alternating the phase between 0or and 180 ° between adjacent strips 1422 and 1424), four distinct phases can be provided, specifically, 0 °, 90 °, 180 °, and 270 °. As illustrated in Figure 17C, the repetitive phase pattern applied through transducer 1420 from left to right can be 90 °, 0 °, 270 ° and 180 °. As illustrated in the intensity graph, in one embodiment, a peak 1438 approximately -1 mm away from a beam axis at a focal depth can be created. In one embodiment, as illustrated in Figure 17D, if the phase pattern has an inverted order of 0 ° (sub-strip 1446), 90 ° (sub-strip 1448), 180 ° (sub-strip 1450), and 270 ° (sub-strip

1452), and then a peak 1458 moves approximately +1 mm away from a beam axis. As illustrated in Figure 17D, the

135 strip 1442 has a phase of 0or and strip 1444 has a 180 ° phase (for example, alternating the phase with respect to strip 1442).

[000198] Figure 18 is a schematic illustration of a switchable two-phase system 1500 according to one embodiment. As illustrated, system 1500 has a source 1502 of AC voltage (or current) that drives discrete phase diverters 1504 (phase diverter of 0or) and 1506 (90 ° phase diverter), switches 1508 and 1510, and transducer portions 1512 and 1514. In one mode, discrete phase diverters 1504 and 1506 can be configured to phase out the voltage signal (or current) of AC supplied by source 1502, so that the resulting signals are 90 ° out of phase. In one embodiment, discrete phase diverters 1504 and 1506 can be configured to excite different portions (eg, strips) of the transducer. The output of discrete phase diverters 1504 and 1506 can be connected to switches 1508 and 1510 that are connected to different portions 1512 and 1514 of the transducer. In one embodiment, switches 1508 and 1510 may cause the phase of the voltage (or current) signal provided by source 1502 to alternate between 0or and 90 ° so that the phase pattern in the transducer reverses the order and causes a focal point to move from one side of the beam axis to the other side of the axis

136 of the beam, as illustrated in Figures 17C-17D. In one embodiment, phase diverters 1504 and 1506 can derive the phase by any suitable value, such as 30 °, 45 °, 120 °, 145 °, 180 °, and so on.

Distribution of therapy using amplitude modulation with displacement [000199] In one embodiment, the modulation or division of an ultrasound beam axially and / or laterally, for example so that multiple linear TCP sequences are created simultaneously, from substantially simultaneously, or sequentially, you may need to supply additional power to a transducer in order to achieve a substantially equal intensity at focal points such as an unmodulated beam. In one embodiment, this increase in power may cause the possibility of excessive heating of the tissue near (pre-focal) and / or distant (post-focal) to the focus. For example, for a given transducer configuration, the division of the ultrasound beam from a focal position of approximately (0, 0, 15 mm) to focal positions of approximately (-0.55 mm, 0.15 mm) and (0.55 mm, 0.15 mm) may need to increase the power supply by approximately 2.2 times in order to produce substantially the same intensity in the two focal positions as the intensity in the unmodulated focal position. In one embodiment, this increase in power can be

137 undesirable. In several modalities, amplitude modulation can be combined with displacement opening techniques to reduce the possibility of excessive tissue heating in pre-focal and post-focal regions. For example, the maximum intensity measured in the prefocal and post-focal regions can be reduced.

<td>[000200] The</td><td>figures 19A-</td><td>-19C</td><td>They are</td><td colspan="2">graphics of</td><td>a</td>

<td>distribution</td><td>of intensity</td><td> 1600</td><td>in</td><td>a</td><td>xy plane</td><td>to</td>

<td>approximately</td><td>e 2 mm before</td><td colspan="2">of the approach</td><td>from</td><td>according to</td><td>a</td>

<td>modality. Do not</td><td>has been applied</td><td colspan="2">modulation to</td><td>a</td><td>transducer</td><td>The</td>

Figure 1600 illustrates that the distribution of the acoustic intensity is symmetric to the axis around a beam axis. In one embodiment, the symmetry is caused by a circular opening of the transducer (for example, a focused circular bowl transducer). The highest intensity regions 1601, 1602, and 1604 are presented along the beam axis at a radius of approximately 0 mm (region 1601), 0.75 mm (region 1602) and 1.0 mm (region 1604). In one embodiment, the maximum intensity is approximately 101 W / cm.2 in the plane with the condition that the opening intensity is approximately 1 W / cm2.

[000201] Figures 20A-20C are graphs of a 1620 intensity distribution in an xy plane at a focal depth according to one modality. In one embodiment, the focal depth may be approximately

138 mm Figures 20A-20C show a significant concentration 1622 in the acoustic intensity in a focal plane. In one embodiment, the diameter of the acoustic distribution has decreased from a 0D of about 3 mm in Figures 20A-20C to a diameter of less than about 0.3 mm at a focal depth. The maximum intensity has been increased to approximately 7.73 kW / cm2, which is approximately 77.3 times greater than the maximum intensity of approximately 2 mm before focusing.

[000202] Figure 21 is a schematic illustration of an amplitude modulation aperture pattern 1630 according to one embodiment. The amplitude modulation pattern 1630 can be placed through an opening. The groups of strips or portions of transducer 1632 may represent an amplitude of +1 (for example, due to the expansion of the transducer material). The groups of strips or portions of transducer 1634 may represent an amplitude of -1 (for example, due to the contraction of the transducer material). As shown, groups 1632 and 1634 can alternate through the opening. The separation distance 1640 may correspond to a spatial period of transitions between +1 and -1 of the transducer material through the opening. In one embodiment, the separation distance 1640 together with a local depth and the operating frequency can determine the distance of the beams divided in the plane

139 focal. In one embodiment, any number of transducer portions may be grouped into groups 1632 and 1634. In one embodiment, the number of portions in groups 1632 and 1634 may be the same. In one embodiment, the number of portions in groups 1632 and 1634 may be different. In one embodiment, amplitude modulation may include more than two levels, such as three (0 and ± 1) or more levels.

[000203] Figures 22A-22C are graphs of an intensity distribution 1650 in an x-plane and of an amplitude modulation aperture pattern of Figure 21 approximately 2 mm before focusing according to one embodiment. In one embodiment, the separation distance is approximately 6 mm for an excitation signal frequency of approximately 7 MHz. In one embodiment, the amplitude modulation pattern 1630 is placed along the axis and to divide the beam by approximately 1.1 mm, as demonstrated by focus points 1652 and 1654. In one embodiment, although the energy distribution has an OD of approximately 3 mm in the x direction increases in the direction and approximately 4 mm. Compared to Figures 19A-19C, the maximum intensity of intensity distribution 1650 is increased by approximately 20% at 112 W / cm2, with the condition that 1 W / cm is placed2 of intensity at the unmodulated focal point. In one embodiment, the amount of power from a split opening may be needed.

140 increase by a factor of approximately 2.2 to achieve substantially similar intensities at two focus points. At a depth of approximately 2 mm before focusing, the maximum intensity can be approximately 246 W / cm2 due to the increase in power. However, because in one embodiment the temperature increases in a tissue are proportional to the increases in intensity, the temperature increase in a pre-focal region may be more than double for a split beam design.

[000204] Figures 23A-23C are graphs of an intensity distribution 1670 in an x plane and of an amplitude modulated aperture pattern of Figure 21 at a focal depth according to one embodiment. In one embodiment, the focal depth may be approximately 15 mm. In one embodiment, the intensity of each of the 1672 and 1674 approaches may be approximately 3.45 kW / cm.2, with the condition that 1 W / cm is placed2 at the unmodulated focal point. As illustrated, two symmetrical beams are presented at the focal positions 1672 (0.55 mm, 0.15 mm) and 1674 (0.55 mm, 0.15 mm). In one embodiment, the intensity distribution at the focal positions 1672 and 1674 is substantially similar to the intensity distribution illustrated in Figure 20A-20C.

[000205] Figure 24 is a schematic illustration of a 1680 amplitude modulation aperture pattern with states

141 move or change them according to a modality. In one embodiment, pattern 1680 is the same as the amplitude modulation function 1630 illustrated in Figure 21 with the exception of state changes. In one embodiment, the amplitude modulation pattern 1680 can be placed through an opening as follows. The separation distance 1688 may comprise a plurality of portions or strips of transducer. Although eight of these portions are shown in Figure 24, the number of portions may be any suitable number, such as less than eight or more than eight. The transducer portions can be individually addressable and can be configured to represent a state of amplitude of -1 and / or +1. As voltage or current is supplied to the transducer, the opening changes state (or shifts) from SI to S2, then from S2 to S3, then from S3 to S4, and so on. As illustrated, in the SI state the plurality of portions across the separation distance 1688 are divided into two groups 1682 (modulation of + 1) and 1684 (modulation of -1). When the transition from state SI to state S2 is made, the plurality of portions across the separation distance 1688 are divided into groups 1692 (modulation of +1) and 1690 and 1694 (modulation of 1). As illustrated, the portion 1681 in the SI state corresponds to +1 and in the S2 state corresponds to -1. When the transition from state S2 to state S3 is made, the

142 plurality of portions across the separation distance 1688 is divided into groups 1702 (+1 modulation) and 1700 and 1704 (-1 modulation). When the transition from state S3 to state S4 is made, the plurality of portions across the separation distance 1688 are divided into groups 1712 (modulation of +1) and 1710 and 1711 (modulation of 1). Consequently, the modulation pattern changes (or moves) through the opening over time. In one embodiment, there are eight unique states if the aperture moves with the same amplitude modulation pattern through the aperture. In one embodiment, the effective intensity can be determined as a weighted time average of the acoustic intensity distribution of each opening state. In one embodiment, the opening changes state (or moves) at a speed sufficient to reduce the possibility of excessive heating of the tissues in a pre-focal and / or post-focal manner. In one embodiment, the separation distance 1688 may include any suitable number of transducer portions. In one embodiment, the number of portions in the groups that correspond to the modulation of +1 and -1 can be the same. In one embodiment, the number of portions in the groups that correspond to the modulation of +1 and -1 may be different. In one embodiment, amplitude modulation may include more than two levels, such as three (0 and ± 1) or more levels.

143 [000206] Figures 25A-25D are graphs of an intensity distribution 1730 in an x-plane and of an amplitude modulated aperture pattern with displacement of Figure 24 approximately 2 mm before focusing according to one embodiment. In one embodiment, the maximum intensity is approximately 71 W / cm.2 which is approximately 37% less than the maximum intensity of an amplitude modulated aperture pattern without displacement (for example, shown in Figure 22A-22C). In one embodiment, this reduction can be significant. Figures 25A-25D illustrate that the number and area of regions experiencing high intensity has been reduced compared to Figure 22A-22C. Regions that receive a significant amount of energy are located in approximately six locations 1731-1736. The intensity distribution graph 1730 illustrates that the degree of energy distribution is reduced, compared to Figure 22A-22C, to approximately 2 mm OD in the x dimension and approximately 3 mm OD in the y dimension. In one embodiment, this reduction can be significant. In one embodiment, the intensity distribution 1730 appears according to the acoustic power that emanates from two openings as the intensity distribution 1730 appears to be a spatially offset sum of the distribution 1600 of Figure 19A-19C. In one embodiment, as illustrated in Figure 25, the possibility of excessive heating of the

144 tissues located before and after the approach is significantly reduced.

[000207] Figures 26A-26C are graphs of an intensity distribution 1750 in an x-plane and of an amplitude-modulated aperture pattern with displacement of Figure 24 at focal depth according to one embodiment. In one embodiment, the focal depth may be approximately 15 mm. In one embodiment, although the intensity distribution before the focus changes substantially (compare Figure 25 with Figure 22A-22C), the intensity distribution 1750 in the focal is substantially similar to the intensity distribution 1670 at the focal depth for the aperture pattern modulated in amplitude without displacement illustrated in Figure 23A-23C. In one embodiment, the peak intensity of the 1750 intensity distribution is reduced (for example, comparing 334 W / cm2, with 345 W / cm2). In one embodiment, in order to obtain the same intensity at the focal depth, it may be necessary to increase the power supplied by a factor of 2.3. The maximum intensity approximately 2 mm before focusing will be 163 W / cm2, which is a substantial reduction with respect to the prediction of 246 W / cm2 (Figure 22A-22C) if the amplitude modulation pattern does not shift through the opening. In one embodiment, maximum acoustic intensity in approaches 1752 and 1754 are concentrated.

145 substantially compared to intensity distribution 1650 in Figure 22A-22C.

[000208] Figure 27A is a schematic illustration of a modulated aperture of amplitude with displacement (two levels ± 1) 1800 according to one embodiment. In one embodiment, schematic 1800 corresponds to pattern 1680 illustrated in Figure 24. Figure 27B is a state transition table 1850 of the schematic of two states 1800 according to one modality.

[000209] Figure 28A is a schematic illustration of an amplitude-modulated aperture with displacement (three levels) 1900 according to one embodiment. Schematic 1900 includes a level 0 1952. In one embodiment, level 0 1952 can be achieved by using a ground terminal or by connecting a resistor to the ground terminal. In one embodiment, level 0 1952 can reduce the amount of high frequency spatial components in a focal area (for example, these components may correspond to grid lobes). In one embodiment, level 0 1952 can reduce spatial frequency transitions in pre-focal and post-focal areas. Figure 28B is a 1950 state transition table of the schematic of three 1900 states according to one embodiment.

[000210] Figure 29A is a schematic illustration of an amplitude-modulated aperture with displacement (four

146 levels) 2000 according to one modality. Schematic 2000 includes two additional levels +0.5 2002 and -0.5 2004. In one mode, doing this can provide similar advantages as adding a level 0. In one mode, amplitude modulation through the aperture provided by schematic 2000 can better approach a sine wave, such that high frequency spatial components are not presented in the focal plan. Figure 29B is a state transition table 2050 of the schematic of three states 1900 according to one embodiment.

[000211] In several embodiments, the number of strips and / or portions of the transducer in a separation distance may be less than or greater than eight. The number of portions selected may depend on the amount of heating reduction desired for tissues located before and / or after focusing. In several modalities, the number of amplitude modulation levels may be greater than four, such as six, eight, ten, and so on.

[000212] There are several advantages of using the modalities of the systems and methods described herein. In one embodiment, amplitude modulation, particularly with displacement, and / or phase shunt techniques can reduce the possibility of excessive pre-focal and postfocal heating. In one embodiment, amplitude modulation, particularly with displacement, and / or techniques of

147 Phase shunt can allow you to divide an ultrasound beam into two or more beams. In one embodiment, amplitude modulation, particularly with displacement and / or phase shunt techniques can approximate two or more ultrasound sources by placing ultrasonic energy at two or more focus locations. In one embodiment, amplitude modulation, particularly with displacement and / or phase shunt techniques can reduce the pain or discomfort experienced by a patient during ultrasound therapy by redistributing acoustic energy away from a focal point. In one embodiment, amplitude modulation, particularly with displacement and / or phase shunt techniques can reduce the therapy time due to the production of multiple TCP.

Imaging systems [000213] In one embodiment, a receiving ultrasound beam former can be used as part of an ultrasound imaging system. In one embodiment, an ultrasound imaging system uses a transmission and reception event to create a line of an ultrasound image. The transmission typically focuses on one location and then the reception processing of the focus system focuses on the same location. In this case, the response of the imaging system is described as:

148 h (t) = Tx (t) * Rx (t) (29) [000214] where h (t) is the spatial response of both the transmission and reception openings, Tx (t) is the response of the opening of transmission, and Rx (t) is the response of the reception opening.

[000215] In one embodiment, an ultrasound imaging system uses dynamic reception approach. In this case, although the transmission ultrasound beam is focused on a spatial location, the transmission system can dynamically change the focus along the axis beam so that each spatial location is focused in depth. This system response is represented as:

h (t-ó) = Tx (t) * Rx (t — δ) (30) [000216] The δ represents the time delay between the received signals that suggests how the focus may change for the reception opening according to the signals They come from deeper depths.

[000217] In one embodiment, a technique for dividing a beam of transmission therapy into multiple approaches through manipulation of aperture amplitude may include receiving beams as well. In one mode, a system can include two

149 transmission approaches (or more), and it is possible to focus on any spatial aperture using a reception aperture such as a linear arrangement where delays can be used to direct and focus the received beam along different axes. This method allows the system to obtain two reception beams with only one transmission. This reduces the time required to visually observe the two beam axes from the reception opening. This system is described as:

hi (t-δ) = Tx (t) * Rxi (t-δ) h2(t-ó) = Tx (t) * Rx2 (t-δ) (31a) (31b) [000218] For example, assuming that the system produces two approaches, at a distance 1.0 mm away from the central axis of the therapy transducer and another -1.0 mm away from the central axis of the transducer of therapy of each at a depth of 15 mm. The ultrasound receiver will be able to create two reception lines, one constantly focused on the 1.0 mm peak and one constantly focused on the -1.0 mm peak. In one embodiment, a receiver can create two reception lines, one constantly focused on the 1.0 mm peak and one constantly focused on the -1.0 mm peak simultaneously.

[000219] In one embodiment, a 2100 method comprises the

150 Steps of:

[000220] transmit multiple approaches with an opening therapy [000221] obtain a signal from each portion of a reception opening arrangement [000222] create multiple reception vectors based on multiple approaches, and [000223] use the vectors of reception to accelerate an algorithm for the formation of images.

[000224] In some modalities, the transmission of multiple approaches can be simultaneous or sequential. In some embodiments, the reception vectors can be used simultaneously or sequentially.

[000225] Some embodiments and examples described herein are examples and do not propose to be limiting to describe the full scope of the compositions and methods of this description. Changes, modifications and equivalent variations of some embodiments, materials, compositions and methods may be made within the scope of the present invention, with substantially similar results.

[000226] While the invention is susceptible to various modifications and alternative forms, specific examples thereof have been shown in the figures and are described herein in detail. However, it will be understood that the invention is not limited to particular forms or methods.

151 particular described, but on the contrary, the invention will cover all these modifications, equivalents and alternatives that fall within the spirit and scope of the various modalities described and the appended claims. Any of the methods described herein may not need to be performed in the order cited. The methods described herein include certain actions taken by a practitioner; however, they may also include any instruction from a third party of those actions, either expressly or by implication. For example, actions such as coupling a transducer module with an ultrasonic probe include instructing the coupling of a transducer module with an ultrasonic probe. The intervals described herein also encompass any and all overlaps, sub-intervals, and combinations thereof. The text such as up to, at least, greater than, less than, between and the like includes the quoted number. Numbers preceded by a term such as approximately or near include the quoted numbers. For example, approximately 25 mm includes 25 mm.

1ΊΊ provide an ultrasonic treatment; and a hand wand adapted to direct ultrasonic treatment in a sequence of individual zones of thermal cosmetic treatment, the hand wand comprising:

a transducer adapted to simultaneously apply ultrasonic therapy to tissue in a plurality of locations at a focal depth with at least one of the group consisting of amplitude modulation, polarization, where different polarization moments are provided in a plurality of portions of the material piezoelectric, and phase shunt, where the plurality of portions of the piezoelectric material is emitted by corresponding signals with different phases, wherein the plurality of portions of the piezoelectric material is adapted to create variations 15 respectively in response to an electric field applied to the ultrasound transducer.

178

SUMMARY

Contents2

90 members in 19 offices

This recordMember, by publication datePriority claim9 more offices are in the list below

Priority claims3

Priority claims
Document	Office	Kind	Date
61774785	United States of America	–	2013-03-08
201361774785	United States of America	P	2013-03-08
2014019633	United States of America	W	2014-02-28

Members90

Family members, oldest first
Document	Office	Kind
CN104027893A	China	A	2014-09-10
US2014257145A1	United States of America	A1	2014-09-11
CA2902063A1	Canada	A1	2014-09-12
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Devices and methods for multi-focus ultrasound therapy.

Abstract

Term

DEVICES AND METHODS FOR MULTIFOCAL ULTRASOUND THERAPY

SUMMARY

Priority claims3

Members90

Events

Numbers

Titles2

Classification