JP2015029664A - Ultrasonic therapy equipment - Google Patents

Ultrasonic therapy equipment Download PDF

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JP2015029664A
JP2015029664A JP2013161064A JP2013161064A JP2015029664A JP 2015029664 A JP2015029664 A JP 2015029664A JP 2013161064 A JP2013161064 A JP 2013161064A JP 2013161064 A JP2013161064 A JP 2013161064A JP 2015029664 A JP2015029664 A JP 2015029664A
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ultrasonic
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誠 橋爪
Makoto Hashizume
誠 橋爪
一 剣持
Hajime Kenmochi
一 剣持
東　隆
Takashi Azuma
隆 東
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Kyushu University NUC
University of Tokyo NUC
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A—HUMAN NECESSITIES
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    • A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36—Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37—Surgical systems with images on a monitor during operation
    • A61B2090/378—Surgical systems with images on a monitor during operation using ultrasound
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0086—Beam steering
    • A61N2007/0095—Beam steering by modifying an excitation signal

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Abstract

PROBLEM TO BE SOLVED: To enable therapy equipment including laminate structure of respective ultrasonic arrays for imaging and for therapy to output a high-accuracy and high-output ultrasonic wave allowing for an efficient therapy.SOLUTION: Ultrasonic therapy equipment 100 includes: a single ultrasonic array for therapy 20 irradiating a subject 10 with an ultrasonic wave for therapy; and an ultrasonic array for imaging 30 laminated on a prescribed region 21 on the single ultrasonic array for therapy 20, irradiating the subject 10 with an ultrasonic wave for imaging, and receiving reflection wave of the ultrasonic wave for imaging. A sound velocity adjustment member 40 having prescribed density is laminated on non-laminate regions 22 where the ultrasonic array for imaging 30 is not laminated, of the ultrasonic array for therapy 20, so that the ultrasonic therapy equipment 100 has configuration for cancelling a difference between respective sound channel lengths leading to the subject 10 from the respective regions of the non-laminate regions 22 and the prescribe region 21.

Description

本発明は、超音波治療装置に関し、特に、撮像用と治療用の各超音波アレイを積層した構造を備える治療装置において、効率的な治療行為が可能となる精度良好で高出力の超音波を出力可能とする技術に関する。   The present invention relates to an ultrasonic therapy apparatus, and in particular, in a therapy apparatus having a structure in which imaging and therapeutic ultrasonic arrays are stacked, ultrasonic waves with high accuracy and high output that enable efficient therapeutic action are provided. It relates to technology that enables output.

カテーテル誘導下で患部に超音波を照射し、そのエネルギーと加温効果とによって肺塞栓や脳梗塞等における血栓溶解効果を加速させる技術や、超音波照射に伴う発熱により癌細胞滅却を図る技術など、照射対象の生体にエネルギーを印加し発熱を生じさせる超音波を用いた各種の治療技術が開発されている。
こうした超音波を用いた治療技術として以下のようなものが提案されている。すなわち、配列された複数の第１の振動素子を含み、被検体に治療用超音波を射出する治療用振動子と、配列された複数の第２の振動素子を含み、前記被検体に診断用超音波を射出し、前記被検体で反射された前記診断用超音波を受信する診断用振動子とを備え、前記治療用振動子と前記診断用振動子とが積層されていることを特徴とする超音波プローブ（特許文献１参照）などが提案されている。 Technology that irradiates the affected area with ultrasound under catheter guidance and accelerates the thrombolytic effect in lung embolism and cerebral infarction by its energy and heating effect, technology that aims to destroy cancer cells by fever accompanying ultrasound irradiation, etc. Various treatment techniques using ultrasonic waves that generate heat by applying energy to a living body to be irradiated have been developed.
The following treatment techniques using such ultrasonic waves have been proposed. That is, a diagnostic transducer including a plurality of arranged first vibration elements and emitting therapeutic ultrasonic waves to the subject and a plurality of arranged second vibration elements, the subject being used for diagnosis A diagnostic vibrator for emitting ultrasonic waves and receiving the diagnostic ultrasonic waves reflected by the subject, wherein the therapeutic vibrator and the diagnostic vibrator are laminated. An ultrasonic probe (see Patent Document 1) is proposed.

また、治療用超音波を被検体内の治療対象に照射する治療用超音波振動子と、前記被検体内の画像を得るために画像用超音波で前記被検体内を走査する画像用超音波探触子と、前記画像用超音波探触子を介して前記治療用超音波の反射波を受信する受信手段と、前記受信手段による受信信号に基づいて前記治療用超音波の強度を制御する制御手段とを具備したことを特徴とする超音波治療装置（特許文献２参照）なども提案されている。
また、超音波機器を最小化し、電磁干渉および放熱を大幅に削減すべく、療法超音波を発生させる圧電トランスデューサと、この圧電トランスデューサを駆動する電力増幅モジュールとを、電力増幅モジュールの放熱板となる筐体内に取り付けた集積超音波療法トランスデューサアセンブリ（特許文献３参照）なども提案されている。 In addition, a therapeutic ultrasonic transducer that irradiates a therapeutic target in a subject with a therapeutic ultrasonic wave, and an ultrasonic image for scanning the inside of the subject with an ultrasonic image for obtaining an image in the subject. A probe; a receiving means for receiving a reflected wave of the therapeutic ultrasonic wave via the imaging ultrasonic probe; and an intensity of the therapeutic ultrasonic wave based on a signal received by the receiving means. An ultrasonic therapy apparatus (see Patent Document 2) characterized by comprising a control means has also been proposed.
In addition, in order to minimize ultrasonic equipment and greatly reduce electromagnetic interference and heat dissipation, a piezoelectric transducer that generates therapy ultrasonic waves and a power amplification module that drives the piezoelectric transducer serve as a heat dissipation plate for the power amplification module. An integrated ultrasonic therapy transducer assembly (see Patent Document 3) mounted in a housing has also been proposed.

ＷＯ２００４／０６６８５６WO2004 / 066856 特開平８−１３１４５４号公報JP-A-8-131454 特開２０１２−０５０８３６号公報JP 2012-050836 A

従来の治療装置においては、診断用超音波を発振する撮像アレイが、治療用超音波を発振する治療アレイ上に積層され、これら２種の超音波アレイを同時に利用可能とする構造を備えるものがある。その場合、該当装置を使用する医師において診断と治療をシームレスに行えるとの有利な特性を備える一方、両アレイ間の接合構造に悪影響を及ぼす懸念から治療アレイの超音波出力を増大させにくい欠点があった。
そこで、図１に示す治療アレイ１のごとく、撮像アレイ２を積層させた第１素子３の周囲に、撮像アレイ２を積層させない第２素子４および第３素子５を追加した構造を採用し、出力不足を補う技術が開発されている。
ところが、上部に撮像アレイを載置した第１素子３と、撮像アレイを載置していない第２素子４、第３素子５とでは実効的な音路長が異なることとなるため、焦点における位相ずれが発生し、患部等の目標物に照射される超音波ビームが劣化するおそれがある。また、上述した第１〜第３の各素子３〜５間の間隙から装置内に水分が浸入することを防止すべく、各素子３〜５のそれぞれの周囲を筐体等に液密に固定する必要がある。こうした構造は、超音波発振に際しての振動効率を各素子３〜５で低下させることにつながり、エネルギー消費の増大や超音波出力の低下等を招く恐れがあるという課題がある。
本発明は、上記のような課題に鑑みなされたものであって、撮像用と治療用の各超音波アレイを積層した構造を備える治療装置において、効率的な治療行為が可能となる精度良好で高出力の超音波を出力可能とする技術を提供することを目的とする。 In a conventional treatment apparatus, an imaging array that oscillates diagnostic ultrasound is stacked on a treatment array that oscillates treatment ultrasound, and has a structure that allows these two types of ultrasound arrays to be used simultaneously. is there. In that case, the doctor who uses the device has an advantageous characteristic that diagnosis and treatment can be performed seamlessly, but there is a drawback that it is difficult to increase the ultrasonic output of the treatment array due to the fear of adversely affecting the joint structure between the two arrays. there were.
Therefore, as in the treatment array 1 shown in FIG. 1, a structure in which the second element 4 and the third element 5 that do not stack the imaging array 2 are added around the first element 3 that stacks the imaging array 2, Technology to compensate for the lack of output has been developed.
However, since the effective sound path length is different between the first element 3 having the imaging array mounted thereon and the second element 4 and the third element 5 having no imaging array mounted thereon, There is a possibility that a phase shift occurs and the ultrasonic beam irradiated to a target such as an affected part deteriorates. In addition, in order to prevent moisture from entering the apparatus through the gap between the first to third elements 3 to 5 described above, the periphery of each element 3 to 5 is fixed in a liquid-tight manner to a housing or the like. There is a need to. Such a structure leads to a decrease in vibration efficiency at the time of ultrasonic oscillation by each of the elements 3 to 5, and there is a problem that an increase in energy consumption and a decrease in ultrasonic output may be caused.
The present invention has been made in view of the above-described problems, and in a treatment apparatus having a structure in which imaging and treatment ultrasonic arrays are stacked, the accuracy of enabling an efficient treatment action is high. An object of the present invention is to provide a technology capable of outputting high-power ultrasonic waves.

上記のような課題を解決するために、本発明は、以下のような手段を採用している。
すなわち、請求項１に係る発明は、被検体に対し治療用超音波を照射する単体の治療用超音波アレイと、前記単体の治療用超音波アレイ上の所定領域に積層され、前記被検体に対し撮像用超音波を照射し当該撮像用超音波の反射波を受信する撮像用超音波アレイとを備え、治療用超音波アレイ上のうち撮像用超音波アレイを積層していない非積層領域に、所定密度を有する音速調整部材を積層し、前記非積層領域及び前記所定領域の各領域から前記被検体に至るそれぞれの音路長の差異をキャンセルする構造を備えることを特徴とする。
本発明の超音波治療装置によれば、治療用超音波アレイと撮像用超音波アレイとの積層構造における各所で実効的な音路長を実質的に同一とし、被検体上の焦点における位相ずれ発生の抑制、ひいては被検体に照射される超音波ビームの精度も良好なものとなる。また、治療用超音波アレイが複数素子ではなく単体の素子からなっているため、表面振幅が従来より大きくなり、超音波出力を増大できる上、従来のように各素子間の間隙からの水分浸入を防止するための構造が不要であるので、超音波発振に際しての振動効率を良好なものとできる。 In order to solve the above problems, the present invention employs the following means.
That is, the invention according to claim 1 is a single therapeutic ultrasonic array that irradiates a subject with therapeutic ultrasonic waves, and is laminated on a predetermined region on the single therapeutic ultrasonic array, An ultrasonic imaging array that irradiates imaging ultrasonic waves and receives reflected waves of the imaging ultrasonic waves, and is disposed in a non-laminated area where the imaging ultrasonic arrays are not stacked on the therapeutic ultrasonic array. And a structure in which sound speed adjusting members having a predetermined density are stacked so as to cancel the difference in sound path length from each of the non-stacked region and the predetermined region to the subject.
According to the ultrasonic therapy apparatus of the present invention, the effective sound path length is substantially the same at various points in the laminated structure of the therapeutic ultrasonic array and the imaging ultrasonic array, and the phase shift at the focal point on the subject Suppression of the generation, and hence the accuracy of the ultrasonic beam irradiated to the subject is also improved. In addition, since the therapeutic ultrasonic array is composed of a single element rather than a plurality of elements, the surface amplitude is larger than before, and the ultrasonic output can be increased. Therefore, the vibration efficiency at the time of ultrasonic oscillation can be improved.

つまり、撮像と治療の各超音波アレイの積層構造を備える治療装置において、効率的な治療行為が可能となる精度良好で高出力の超音波を出力することができる。
また、請求項２に係る発明は、請求項１に記載の超音波治療装置であって、前記非積層領域に積層した前記音速調整部材として、前記非積層領域上に配線された前記撮像用超音波アレイの接続ケーブルも含むことを特徴とする。
本発明の超音波治療装置によれば、前記非積層領域及び前記所定領域の各領域から前記被検体に至るそれぞれの音路長の差異をより高い精度でキャンセルすることにつながり、実効的な音路長の同一化も更に精度良く図られることとなる。
さらに、請求項３に係る発明は、請求項１または２に記載の超音波治療装置であって、被検体に対し治療用超音波を照射する複数の素子からなる治療用超音波アレイと、前記複数の素子のうちいずれかの素子上に積層され、前記被検体に対し撮像用超音波を照射し当該撮像用超音波の反射波を受信する撮像用超音波アレイとを備え、上部に撮像用超音波アレイを積層した積層対象素子と、撮像用超音波アレイを積層していない非積層対象素子とで、素子に印加する駆動電圧の位相を所定程度相違させ、前記各素子から前記被検体に至るそれぞれの音路長の差異をキャンセルする、位相調整手段を備えることを特徴とする。 In other words, in a treatment apparatus having a laminated structure of imaging and treatment ultrasonic arrays, it is possible to output high-accuracy and high-accuracy ultrasonic waves that enable efficient treatment.
Further, the invention according to claim 2 is the ultrasonic therapy apparatus according to claim 1, wherein the imaging ultrasonic superimposing member wired on the non-laminated area is used as the sound velocity adjusting member laminated on the non-laminated area. A connection cable for the acoustic wave array is also included.
According to the ultrasonic therapy apparatus of the present invention, it is possible to cancel the difference in sound path length from each region of the non-stacked region and the predetermined region to the subject with higher accuracy, and effective sound. The same road length can be achieved with higher accuracy.
Further, the invention according to claim 3 is the ultrasonic therapy apparatus according to claim 1 or 2, wherein the therapeutic ultrasonic array comprising a plurality of elements for irradiating the subject with therapeutic ultrasonic waves, An imaging ultrasonic array that is stacked on any one of a plurality of elements and irradiates the subject with imaging ultrasound and receives reflected waves of the imaging ultrasound; The phase of the driving voltage applied to the element is different by a predetermined degree between the stacking target element in which the ultrasonic array is stacked and the non-stacking target element in which the imaging ultrasonic array is not stacked. It is characterized by comprising phase adjusting means for canceling the difference in the respective sound path lengths.

本発明の超音波治療装置によれば、治療用超音波アレイが複数の素子からなる構造において、超音波出力を大きなものとしても、各素子に印加する駆動電圧の位相を調整することにより、各所で実効的な音路長を同一とし、被検体上の焦点における位相ずれ発生の抑制、ひいては被検体に照射される超音波ビームの精度も良好なものとなる。つまり、撮像用と治療用の各超音波アレイを積層する構造を備える治療装置において、効率的な治療行為が可能となる精度良好で高出力の超音波を出力することができる。   According to the ultrasonic therapy apparatus of the present invention, in a structure in which the therapeutic ultrasonic array is composed of a plurality of elements, even if the ultrasonic output is large, by adjusting the phase of the drive voltage applied to each element, Thus, the effective sound path length is made the same, the occurrence of phase shift at the focal point on the subject is suppressed, and the accuracy of the ultrasonic beam applied to the subject is also improved. That is, in a treatment apparatus having a structure in which imaging and treatment ultrasonic arrays are stacked, it is possible to output high-accuracy ultrasonic waves with good accuracy that enable efficient treatment.

以上説明したように、本発明の超音波治療装置によれば、撮像用と治療用の各超音波アレイを積層する構造を備える治療装置において、効率的な治療行為が可能となる精度良好で高出力の超音波を出力することが可能となる。   As described above, according to the ultrasonic treatment apparatus of the present invention, in the treatment apparatus having a structure in which the ultrasonic arrays for imaging and treatment are stacked, the accuracy is high and the efficient treatment action is possible. It becomes possible to output an output ultrasonic wave.

従来の超音波治療装置における撮像アレイと治療アレイの積層構造例を示す図である。It is a figure which shows the laminated structure example of the imaging array and treatment array in the conventional ultrasonic therapy apparatus. 第１実施形態の超音波治療装置の構成例を示す断面図である。It is sectional drawing which shows the structural example of the ultrasonic therapy apparatus of 1st Embodiment. 焦点面上でのビーム形状の例を示すグラフである。It is a graph which shows the example of the beam shape on a focal plane. 第２実施形態の超音波治療装置の構成例を示す断面図である。It is sectional drawing which shows the structural example of the ultrasonic therapy apparatus of 2nd Embodiment.

−−−第１の形態−−−
以下、図面を参照しながら本発明の実施の形態について説明する。図２は、第１実施形態の超音波治療装置１００の構成例を示す断面図である。第１実施形態における超音波治療装置１０は、図２にて示すような、複数素子から構成されず、従って単体である治療用超音波アレイ２０と、治療用超音波アレイ２０上に配置した撮像用超音波アレイ３０との積層構造２００と、こうした各超音波アレイ２０、３０の制御機能とを備えている。ここで、制御機能としては、例えば、治療用超音波アレイ２０に接続された治療用アレイ駆動部２５と、撮像用超音波アレイ３０に接続された撮像用超音波送受部３１および画像処理部３２と、表示部１０５とが含まれる。
このうち、治療用アレイ駆動部２５は、治療用超音波アレイ２０に治療用超音波を発振させる駆動電圧を生成、印加する回路である。また、撮像用超音波送受部３１は、撮像用超音波アレイ３０に撮像用超音波を発振させる駆動電圧を生成、印加する一方、被検体１０から返される反射エコー波を受信する回路である。また、画像処理部３２は、前述の反射エコー波に基づき画像生成を行う回路である。また、表示部１０５は、上述した反射エコー波から画像処理部が３２が生成した被検体１０の画像を表示するディスプレイ装置である。なお、治療用アレイ駆動部２５と撮像用超音波送受部３１は、ノイズが発生しないように、治療用超音波アレイ２０と撮像用超音波アレイ３０とにおいて所定の設定時間（例：撮像用超音波は１秒以内程度、治療用超音波は１０秒以内程度）ごとに交互に超音波を射出するよう、駆動電圧の印可制御を行うものとなる。 --- First form ---
Hereinafter, embodiments of the present invention will be described with reference to the drawings. FIG. 2 is a cross-sectional view illustrating a configuration example of the ultrasonic therapy apparatus 100 according to the first embodiment. The ultrasonic therapy apparatus 10 according to the first embodiment is not composed of a plurality of elements as shown in FIG. 2, and therefore is a single therapeutic ultrasonic array 20 and an imaging arranged on the therapeutic ultrasonic array 20. And the control structure of each of the ultrasonic arrays 20 and 30 are provided. Here, as control functions, for example, the therapeutic array drive unit 25 connected to the therapeutic ultrasonic array 20, the imaging ultrasonic transmission / reception unit 31 and the image processing unit 32 connected to the imaging ultrasonic array 30 are used. And a display unit 105.
Among these, the therapeutic array driving unit 25 is a circuit that generates and applies a driving voltage for causing the therapeutic ultrasonic array 20 to oscillate therapeutic ultrasonic waves. The imaging ultrasonic transmission / reception unit 31 is a circuit that generates and applies a drive voltage for oscillating imaging ultrasound to the imaging ultrasound array 30 and receives a reflected echo wave returned from the subject 10. The image processing unit 32 is a circuit that generates an image based on the above-described reflected echo wave. The display unit 105 is a display device that displays an image of the subject 10 generated by the image processing unit 32 from the above-described reflected echo waves. The therapeutic array driving unit 25 and the imaging ultrasonic transmission / reception unit 31 have a predetermined set time (e.g., imaging ultrasonic array) in the therapeutic ultrasonic array 20 and the imaging ultrasonic array 30 so that noise is not generated. The application control of the driving voltage is performed so that the ultrasonic waves are alternately emitted every 1 second or less and the therapeutic ultrasonic waves are within 10 seconds.

また、上述の積層構造２００を構成する治療用超音波アレイ２０および撮像用超音波アレイ３０のうち、治療用超音波アレイ２０は約３ＭＨｚの超音波を発振し、撮像用超音波アレイ３０はそれよりも高い周波数の、約１０ＭＨｚの超音波を発振する。撮像用超音波アレイ３０が生じる高い周波数の超音波は、治療用超音波アレイ２０が生じる低い周波数の超音波よりも物体透過能力が低い。そのため、治療用超音波アレイ２０上に撮像用超音波アレイ３０を積層した構造となっている。
また、治療用超音波アレイ２０と撮像用超音波アレイ３０との間には、周波数選択性音響分離層１５が設けられている。この周波数選択性音響分離層１５は、治療用超音波アレイ２０と撮像用超音波アレイ３０とで音響インピーダンスの差異を十分大きくすることで設けられる層であり、治療用超音波アレイ２０にとっては不要な反射エコー波が治療用超音波アレイ２０にまで到達して治療用超音波の出力に悪影響を与えることを抑止する一方、治療用超音波アレイ２０による治療用超音波は撮像用超音波アレイ３０を透過して被検体１０に向けて進むことを阻害しない機能を発揮する。 Of the therapeutic ultrasonic array 20 and imaging ultrasonic array 30 constituting the laminated structure 200 described above, the therapeutic ultrasonic array 20 oscillates about 3 MHz ultrasonic waves, and the imaging ultrasonic array 30 An ultrasonic wave of about 10 MHz having a higher frequency is oscillated. The high frequency ultrasonic waves generated by the imaging ultrasonic array 30 have a lower object transmission capability than the low frequency ultrasonic waves generated by the therapeutic ultrasonic array 20. Therefore, the imaging ultrasonic array 30 is stacked on the therapeutic ultrasonic array 20.
A frequency selective acoustic separation layer 15 is provided between the therapeutic ultrasonic array 20 and the imaging ultrasonic array 30. This frequency selective acoustic separation layer 15 is a layer provided by sufficiently increasing the difference in acoustic impedance between the therapeutic ultrasonic array 20 and the imaging ultrasonic array 30 and is not necessary for the therapeutic ultrasonic array 20. While the reflected echo waves reach the therapeutic ultrasonic array 20 and detrimentally affect the output of the therapeutic ultrasonic wave, the therapeutic ultrasonic waves generated by the therapeutic ultrasonic array 20 are the imaging ultrasonic array 30. The function of not impeding the passage of the light toward the subject 10 is shown.

なお、治療用超音波アレイ２０および撮像用超音波アレイ３０は、いずれも所定程度屈曲ないし湾曲した凹板状の圧電セラミックスで形成されている。治療用超音波アレイ２０は、治療用アレイ駆動部２５から印可された駆動電圧を機械的振動に変換し、被検体１０に治療用の超音波を偏向射出する。また、撮像用超音波アレイ３０は、撮像用超音波送受部３１から印可された駆動電圧を機械的振動に変換し、被検体１０に対して撮像用超音波を偏向送波すると共に、被検体１０から発生する反射エコー波を受信して電気信号に変換する。
治療用超音波アレイ２０から射出された治療用超音波の経路は、治療用超音波アレイ２０上で撮像用超音波アレイ３０が積層された積層領域２１から被検体１０に至る第１経路１１と、非積層領域２２から被検体１０に至る第２経路１２、第３経路１３とが存在する。撮像用超音波アレイ３０が経路中に含まれる第１経路１１と、撮像用超音波アレイ３０が経路中に含まれない第２経路１２および第３経路とでは超音波の伝達速度が異なり、ひいては音路長にも差異が生じる。 The therapeutic ultrasonic array 20 and the imaging ultrasonic array 30 are both formed of a concave plate-shaped piezoelectric ceramic that is bent or curved to a predetermined extent. The therapeutic ultrasonic array 20 converts the drive voltage applied from the therapeutic array drive unit 25 into mechanical vibration, and deflects and emits therapeutic ultrasonic waves to the subject 10. The imaging ultrasonic array 30 converts the drive voltage applied from the imaging ultrasonic transmission / reception unit 31 into mechanical vibration, deflects and transmits the imaging ultrasonic waves to the subject 10, and the subject. The reflected echo wave generated from 10 is received and converted into an electric signal.
The path of the therapeutic ultrasound emitted from the therapeutic ultrasound array 20 is the first path 11 from the stacked region 21 where the imaging ultrasound array 30 is stacked on the therapeutic ultrasound array 20 to the subject 10. The second path 12 and the third path 13 from the non-stacked region 22 to the subject 10 exist. The ultrasonic transmission speed is different between the first path 11 in which the imaging ultrasonic array 30 is included in the path and the second path 12 and the third path in which the imaging ultrasonic array 30 is not included in the path. There is also a difference in the sound path length.

そこで第１実施形態の超音波治療装置１００においては、治療用超音波アレイ２０上のうち撮像用超音波アレイ３０を積層していない非積層領域２２には、所定密度を有する音速調整部材４０が積層された構造を備えている。この音速調整部材４０は、例えば厚さ２５０μｍのポリイミド材４１上に、厚さ５０μｍで所定形状の銅材４２を設置した構造となっている。勿論、こうした音速調整部材４０の構造や使用部材の選定に際しては、撮像用超音波アレイ３０が治療用超音波の速度に影響を与えるレベルを事前に解析ないし推定しておき、この解析ないし推定の結果が示す（第２、第３経路の速度と比較した）速度低下ないし速度上昇の値をキャンセルする、すなわち反対の速度上昇ないし速度低下を図れるものを適宜選択すればよい。こうした速度調整部材４０を採用して各経路１１〜１３における超音波速度の統一を図ることで、各経路１１〜１３の音路長に差異が生じることを抑止できる。
各経路１１〜１３の音路長を同一とすれば、被検体１０上の焦点における治療用超音波の位相ずれ発生の抑制、ひいては被検体１０に照射される治療用超音波ビームの精度も良好なものとなる。なお、非積層領域２２に積層した速度調整部材４０として、非積層領域２２上に配線された撮像用超音波アレイ３０の接続ケーブル３３（駆動電圧や反射エコー波の受信信号の経路となる）の材質、サイズも含めて考慮すれば、上述した音路長の同一化が更に高精度なものとなり、被検体１０上の焦点における治療用超音波の位相ずれ発生の抑制、ひいては被検体１０に照射される治療用超音波ビームの精度も更に良好なものとなる。 Therefore, in the ultrasonic therapy apparatus 100 according to the first embodiment, the sonic speed adjusting member 40 having a predetermined density is provided in the non-stacked region 22 where the imaging ultrasonic array 30 is not stacked in the therapeutic ultrasonic array 20. It has a laminated structure. The sonic speed adjusting member 40 has a structure in which, for example, a copper material 42 having a thickness of 50 μm and a predetermined shape is installed on a polyimide material 41 having a thickness of 250 μm. Of course, when selecting the structure of the sound speed adjusting member 40 or the member to be used, the level at which the imaging ultrasonic array 30 affects the speed of the therapeutic ultrasonic wave is analyzed or estimated in advance, and this analysis or estimation is performed. It is only necessary to appropriately select a value that cancels the value of the speed decrease or speed increase (compared to the speeds of the second and third paths) indicated by the result, that is, the opposite speed increase or speed decrease. By adopting such a speed adjusting member 40 to unify the ultrasonic velocity in each of the paths 11 to 13, it is possible to prevent a difference in the sound path length of each of the paths 11 to 13.
If the sound path lengths of the paths 11 to 13 are the same, the generation of the phase shift of the therapeutic ultrasonic wave at the focal point on the subject 10 is suppressed, and the accuracy of the therapeutic ultrasonic beam irradiated to the subject 10 is also good. It will be something. In addition, as the speed adjusting member 40 laminated on the non-laminated area 22, a connection cable 33 (which serves as a path for a reception signal of a drive voltage or a reflected echo wave) of the imaging ultrasonic array 30 wired on the non-laminated area 22 is used. If the material and size are taken into consideration, the above-described sound path length identification becomes even more accurate, suppressing the occurrence of a phase shift of the therapeutic ultrasonic wave at the focal point on the subject 10, and thus irradiating the subject 10 The accuracy of the therapeutic ultrasonic beam to be applied is further improved.

図３に焦点面上でのビーム形状の例を示す。同図は、周波数３ＭＨz、曲率半径（焦点距離）３０ｍｍ、口径幅１５ｍｍ、治療素子上の撮像素子の口径幅を短軸５ｍｍ、長軸１５ｍｍとしたときに計算の結果、得られたビーム形状である。同図では、治療素子から直接焦点に到達した経路と、撮像素子を通った経路のそれぞれに位相差を０度（本発明）、４５度、６０度、９０度、１３５度、１８０度のそれぞれの場合について焦点面上でのビーム形状をプロットしてある。ここで、各図の横軸はビームの焦点からの方位方向への距離（ｍｍ）、縦軸はビームの強度（単位なし）を示している 。実線は撮像素子の短軸に平行な方向、破線は撮像素子の長軸に平行な方向に沿ったプロットである。ビーム強度は位相差０度のときの最大値で規格化してある。この結果から、位相差によっては最大音圧が７０％程度に低下し（エネルギーは音圧の二乗に比例するので、このときのエネルギーは半分となる）、ピークの位置が２ｍｍ弱ずれていることが確認できる。このように実効的な音路長を一定とする本発明の効果が図の計算結果からも確認できる。
第１実施形態においては、治療用超音波アレイ２０が複数素子ではなく単体の素子からなっているため、治療用超音波発振時の表面振幅が従来（複数素子のそれぞれで発振）より大きくなり、超音波出力を増大できる上、従来のように各素子間の間隙からの水分浸入を防止するための構造は不要で、超音波発振に際しての振動効率を良好なものとできる。ここで、口径の中心で最大音圧、端で０になる音圧分布をハニング関数 （0.5-0.5cos(2px)；0<x<1）に近似すると、本発明による場合と比べて、従来技術のように素子が三つに分かれている場合は、素子表面の音圧の積分値が５１％に低下、すなわちエネルギーに換算すると２６％にまで低下してしまう（ここでは、三つの素子に分割された場合の音圧分布を、３つ並んだハニング関数と、全体を覆う一つのハニング関数の積から概算した。）。治療用超音波アレイ２０を複数素子で構成した従来の超音波治療装置における超音波出力は、１０Ｗ／ｃｍ２であったが、第１実施形態の超音波治療装置１００における超音波出力は、１ｋＷ／ｃｍ２となり、他の不具合無く高出力を実現できた。 FIG. 3 shows an example of the beam shape on the focal plane. This figure shows the beam shape obtained as a result of calculation when the frequency is 3 MHz, the radius of curvature (focal length) is 30 mm, the aperture width is 15 mm, and the aperture width of the imaging device on the treatment element is 5 mm short axis and 15 mm long axis. is there. In the figure, the phase difference is 0 degree (invention), 45 degrees, 60 degrees, 90 degrees, 135 degrees, and 180 degrees, respectively, on the path that directly reaches the focal point from the treatment element and the path that passes through the imaging element. The beam shape on the focal plane is plotted for. Here, the horizontal axis of each figure indicates the distance (mm) in the azimuth direction from the focal point of the beam, and the vertical axis indicates the intensity of the beam (no unit). A solid line is a plot along a direction parallel to the short axis of the image sensor, and a broken line is a plot along a direction parallel to the long axis of the image sensor. The beam intensity is normalized by the maximum value when the phase difference is 0 degree. From this result, the maximum sound pressure decreases to about 70% depending on the phase difference (the energy is proportional to the square of the sound pressure, so the energy at this time is halved), and the peak position is shifted slightly less than 2 mm. Can be confirmed. Thus, the effect of the present invention that makes the effective sound path length constant can also be confirmed from the calculation results of the figure.
In the first embodiment, since the therapeutic ultrasonic array 20 is composed of a single element rather than a plurality of elements, the surface amplitude at the time of therapeutic ultrasonic oscillation is larger than the conventional (oscillated by each of the plurality of elements), In addition to increasing the ultrasonic output, the conventional structure for preventing moisture intrusion from the gap between the elements is unnecessary, and the vibration efficiency at the time of ultrasonic oscillation can be improved. Here, when the sound pressure distribution at the center of the caliber is approximated to the Hanning function (0.5-0.5cos (2px); 0 <x <1) When the element is divided into three as in the technology, the integrated value of the sound pressure on the element surface is reduced to 51%, that is, to 26% when converted to energy (here, the three elements are divided into three elements). The sound pressure distribution when divided was estimated from the product of three Hanning functions lined up and one Hanning function covering the whole.) The ultrasonic output in the conventional ultrasonic therapeutic apparatus in which the therapeutic ultrasonic array 20 is composed of a plurality of elements is 10 W / cm 2 , but the ultrasonic output in the ultrasonic therapeutic apparatus 100 of the first embodiment is 1 kW. / Cm 2 , and high output could be realized without other problems.

−−−第２の形態−−−
図４は第２実施形態の超音波治療装置の構成例を示す断面図である。続いて、治療用超音波アレイが複数の素子からなる従来の構造において、被検体１０上の焦点における位相ずれ発生の抑制、ひいては被検体１０に照射される超音波ビームの精度を良好なものとする技術について説明する。
この場合、超音波治療装置１００における治療用超音波アレイ５０は、複数の素子、すなわち第１素子５１、第２素子５２、第３素子５３から構成されている。また、第１〜第３の各素子５１〜５３のうち、例えば第１素子５１上には撮像用超音波アレイ３０が積層された構造となっている。この第１素子５１を、その上部に撮像用超音波アレイ３０を積層した積層対象素子とする。他方、撮像用超音波アレイ３０を積層していないその他の素子すなわち第２素子５２、第３素子５３は非積層対象素子とする。
なお、治療用超音波アレイ５０を構成する第１素子５１、第２素子５２、第３素子５３のそれぞれは、各治療用アレイ駆動部２５Ａ〜２５Ｃに接続されており、独立に駆動することができる構成となっている。一方、撮像用超音波アレイ３０の構成とその駆動制御の機能等については上述した第１実施形態と同様である。また、治療用超音波アレイ５０を構成する第１〜第３の各素子５１〜５３と撮像用超音波アレイ３０の形状、材質（凹板状の圧電セラミックス）や機能、および、治療用超音波アレイ２０と撮像用超音波アレイ３０との間に設ける周波数選択性音響分離層１５の存在等も上述した第１実施形態と同様である。 --- Second form ---
FIG. 4 is a cross-sectional view illustrating a configuration example of the ultrasonic therapy apparatus according to the second embodiment. Subsequently, in the conventional structure in which the therapeutic ultrasonic array is composed of a plurality of elements, the occurrence of phase shift at the focal point on the subject 10 is suppressed, and the accuracy of the ultrasonic beam irradiated to the subject 10 is improved. The technology to do is explained.
In this case, the therapeutic ultrasound array 50 in the ultrasound treatment apparatus 100 is composed of a plurality of elements, that is, a first element 51, a second element 52, and a third element 53. In addition, among the first to third elements 51 to 53, for example, the imaging ultrasonic array 30 is stacked on the first element 51. The first element 51 is a stack target element in which the imaging ultrasonic array 30 is stacked on the first element 51. On the other hand, other elements on which the imaging ultrasonic array 30 is not stacked, that is, the second element 52 and the third element 53 are non-stacked elements.
Each of the first element 51, the second element 52, and the third element 53 constituting the therapeutic ultrasonic array 50 is connected to each of the therapeutic array driving units 25A to 25C and can be driven independently. It can be configured. On the other hand, the configuration of the imaging ultrasonic array 30 and its drive control function are the same as those in the first embodiment. Further, the shape, material (concave plate-shaped piezoelectric ceramic) and function of the first to third elements 51 to 53 and the imaging ultrasonic array 30 constituting the therapeutic ultrasonic array 50, and the therapeutic ultrasonic waves. The presence of the frequency selective acoustic separation layer 15 provided between the array 20 and the imaging ultrasonic array 30 is the same as in the first embodiment described above.

第２実施形態の超音波治療装置１００において、積層対象素子たる第１素子５１から被検体１０に至る第１経路１１と、非積層対象素子たる第２素子５２から被検体１０に至る第２経路１２、および非積層対象素子たる第３素子５３から被検体１０に至る第３経路１３とでは、超音波の伝達速度が異なり、ひいては音路長にも差異が生じてしまう。
そこで第２実施形態の超音波治療装置１００においては、上述した積層対象素子たる第１素子５１と、非積層対象素子たる第２素子５３および第３素子５３とで、治療用アレイ駆動部２５（位相調整手段）により素子に印加する駆動電圧の位相を所定程度相違させ、第１経路１１と、第２経路１２および第３経路１３との間での、音路長の差異をキャンセルする。
具体的には、撮像アレイを構成する材料がN種類の場合（N＝３〜５）に、各層の厚みと音速をそれぞれｔ１、ｔ2、・・・、ｔN、ｃ１、ｃ2、・・・ｃN、水の音速をｃWとすると、積層された素子での音路長と、積層されない素子の音路長それぞれの伝搬時間の差Δｔは次式のようになるので、
Δｔ＝（t1/c1＋t2/c2＋・・・＋ｔN/cN）-（ｔ１＋ｔ2＋・・・＋ｔN）/ｃW
このΔｔをキャンセルするように、周波数がfの場合はΔｔ×ｆの位相差を設定すればよい。 In the ultrasonic therapy apparatus 100 according to the second embodiment, a first path 11 from the first element 51 as a stacking target element to the subject 10 and a second path from the second element 52 as a non-stacking target element to the subject 10. 12 and the third path 13 from the third element 53, which is a non-stacking target element, to the subject 10, the transmission speed of the ultrasonic waves is different, and the sound path length is also different.
Therefore, in the ultrasonic therapy apparatus 100 according to the second embodiment, the therapeutic array driving unit 25 (the first element 51 as the stacking target element and the second element 53 and the third element 53 as the non-stacking target elements described above are used. The phase of the driving voltage applied to the element is made to differ by a predetermined amount by the phase adjusting means), and the difference in sound path length between the first path 11, the second path 12, and the third path 13 is canceled.
Specifically, when there are N kinds of materials constituting the imaging array (N = 3 to 5), the thickness and sound velocity of each layer are t1, t2,..., TN, c1, c2,. If the sound velocity of water is cW, the difference Δt in the propagation time between the sound path length of the stacked elements and the sound path length of the non-stacked elements is as follows:
Δt = (t1 / c1 + t2 / c2 + ... + tN / cN)-(t1 + t2 + ... + tN) / cW
In order to cancel this Δt, when the frequency is f, a phase difference of Δt × f may be set.

勿論、こうした駆動電圧の位相設定に際しては、撮像用超音波アレイ３０が治療用超音波の速度に影響を与えるレベルを事前に解析ないし推定しておき、この解析ないし推定の結果が示す（第２、第３経路の速度と比較した）速度低下ないし速度上昇の値をキャンセルする、すなわち反対の速度上昇ないし速度低下を図れる位相の設定内容を適宜選択すればよい。こうして各経路１１〜１３における速度の統一を図ることで、各経路１１〜１３の音路長に差異が生じることを抑止できる。
各経路１１〜１３の音路長を同一とすれば、被検体１０上の焦点における治療用超音波の位相ずれ発生の抑制、ひいては被検体１０に照射される治療用超音波ビームの精度も良好なものとなる。
以上本実施形態によれば、撮像と治療の各超音波アレイの積層構造を備える治療装置において、効率的な治療行為が可能となる精度良好で高出力の超音波を出力することが可能とる。 Of course, in setting the phase of the driving voltage, the level at which the imaging ultrasonic array 30 affects the speed of the therapeutic ultrasonic wave is analyzed or estimated in advance, and the result of this analysis or estimation is shown (second). The setting content of the phase that cancels the value of the speed decrease or speed increase (compared with the speed of the third path), that is, the opposite speed increase or speed decrease, may be selected as appropriate. Thus, by unifying the speed in each path 11-13, it can suppress that a difference arises in the sound path length of each path 11-13.
If the sound path lengths of the paths 11 to 13 are the same, the generation of the phase shift of the therapeutic ultrasonic wave at the focal point on the subject 10 is suppressed, and the accuracy of the therapeutic ultrasonic beam irradiated to the subject 10 is also good. It will be something.
As described above, according to the present embodiment, it is possible to output high-accuracy and high-accuracy ultrasonic waves that enable an efficient therapeutic action in a treatment apparatus including a stacked structure of imaging and treatment ultrasonic arrays.

１０ 被検体
１１ 第１経路
１２ 第２経路
１３ 第３経路
１５ 周波数選択性音響分離層
２０ 単体の治療用超音波アレイ
２１ 治療用超音波アレイ上の積層領域（所定領域）
２２ 治療用超音波アレイ上の非積層領域
２５ 治療用アレイ駆動部（位相調整手段）
３０ 撮像用超音波アレイ
３１ 撮像用超音波送受部
３２ 画像処理部
３３ 接続ケーブル
４０ 音速調整部材
５０ 治療用超音波アレイ
５１ 第１素子（積層対象素子）
５２ 第２素子（非積層対象素子）
５３ 第３素子（非積層対象素子）
１００ 超音波治療装置
１０５ 表示部
２００ 超音波アレイ積層構造 DESCRIPTION OF SYMBOLS 10 Subject 11 1st path | route 12 2nd path | route 13 3rd path | route 15 Frequency selective acoustic separation layer 20 Single-piece | unit ultrasonic array 21 for therapeutic treatment Laminated area | region (predetermined area | region) on a therapeutic ultrasonic array
22 Non-stacked area 25 on therapeutic ultrasonic array 25 Treatment array drive unit (phase adjustment means)
30 Ultrasonic array for imaging 31 Ultrasonic transmitting / receiving unit for imaging 32 Image processing unit 33 Connection cable 40 Sonic adjustment member 50 Ultrasonic array for treatment 51 First element (stacking target element)
52 2nd element (non-stacking target element)
53 3rd element (non-stacking target element)
DESCRIPTION OF SYMBOLS 100 Ultrasonic therapy apparatus 105 Display part 200 Ultrasonic array laminated structure

Claims (3)

被検体に対し治療用超音波を照射する単体の治療用超音波アレイと、前記単体の治療用超音波アレイ上の所定領域に積層され、前記被検体に対し撮像用超音波を照射し当該撮像用超音波の反射波を受信する撮像用超音波アレイとを備え、
治療用超音波アレイ上のうち撮像用超音波アレイを積層していない非積層領域に、所定密度を有する音速調整部材を積層し、前記非積層領域及び前記所定領域の各領域から前記被検体に至るそれぞれの音路長の差異をキャンセルする構造を備えることを特徴とする超音波治療装置。 A single therapeutic ultrasound array that irradiates the subject with therapeutic ultrasound and a predetermined area on the single therapeutic ultrasound array, and the imaging is performed by irradiating the subject with imaging ultrasound. An ultrasonic imaging array for receiving reflected ultrasonic waves, and
A sound speed adjusting member having a predetermined density is stacked on a non-stacked area on which the imaging ultrasonic array is not stacked on the therapeutic ultrasonic array, and the subject from each of the non-stacked area and the predetermined area is applied to the subject. An ultrasonic therapy apparatus comprising a structure that cancels a difference in the respective sound path lengths. 前記非積層領域に積層した前記速度調整部材として、前記非積層領域上に配線された前記撮像用超音波アレイの接続ケーブルも含むことを特徴とする請求項１に記載の超音波治療装置。   The ultrasonic therapy apparatus according to claim 1, further comprising a connection cable of the imaging ultrasonic array wired on the non-stacked area as the speed adjustment member stacked on the non-stacked area. 被検体に対し治療用超音波を照射する複数の素子からなる治療用超音波アレイと、前記複数の素子のうちいずれかの素子上に積層され、前記被検体に対し撮像用超音波を照射し当該撮像用超音波の反射波を受信する撮像用超音波アレイとを備え、
上部に撮像用超音波アレイを積層した積層対象素子と、撮像用超音波アレイを積層していない非積層対象素子とで、素子に印加する駆動電圧の位相を所定程度相違させ、前記各素子から前記被検体に至るそれぞれの音路長の差異をキャンセルする、位相調整手段を備えることを特徴とする超音波治療装置。 A therapeutic ultrasonic array composed of a plurality of elements that irradiate the subject with therapeutic ultrasonic waves, and is laminated on any one of the plurality of elements, and irradiates the subject with imaging ultrasonic waves. An imaging ultrasonic array that receives a reflected wave of the imaging ultrasonic wave,
The phase of the driving voltage applied to the element is different by a predetermined degree between the stacking target element having the imaging ultrasonic array stacked thereon and the non-stacking target element without the imaging ultrasonic array being stacked. An ultrasonic therapy apparatus comprising phase adjusting means for canceling a difference in sound path lengths reaching the subject.
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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR101935375B1 (en) * 2016-02-01 2019-01-07 서강대학교산학협력단 Ultrasonic therapy apparatus for high intensity focused ultrasound and ultrasound image and the control method thereof

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS61206434A (en) * 1985-03-12 1986-09-12 富士通株式会社 Ultrasonic diagnostic apparatus
JPH04273699A (en) * 1991-02-28 1992-09-29 Toshiba Corp Ultrasonic wave checking device
JP2004154205A (en) * 2002-11-05 2004-06-03 Hitachi Ltd Ultrasonic device
JP2009503990A (en) * 2005-07-26 2009-01-29 アー．ヤー． アンゲルセン、ビョルン Dual frequency ultrasonic transducer array

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH03151952A (en) * 1989-11-08 1991-06-28 Matsushita Electric Ind Co Ltd Apparatus for ultrasonic therapy
JP4263575B2 (en) * 2003-10-02 2009-05-13 株式会社日立メディコ Ultrasonic transmitter and ultrasonic apparatus using the same

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS61206434A (en) * 1985-03-12 1986-09-12 富士通株式会社 Ultrasonic diagnostic apparatus
JPH04273699A (en) * 1991-02-28 1992-09-29 Toshiba Corp Ultrasonic wave checking device
JP2004154205A (en) * 2002-11-05 2004-06-03 Hitachi Ltd Ultrasonic device
JP2009503990A (en) * 2005-07-26 2009-01-29 アー．ヤー． アンゲルセン、ビョルン Dual frequency ultrasonic transducer array

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR101935375B1 (en) * 2016-02-01 2019-01-07 서강대학교산학협력단 Ultrasonic therapy apparatus for high intensity focused ultrasound and ultrasound image and the control method thereof
US11596379B2 (en) 2016-02-01 2023-03-07 Sogang University Research Foundation Ultrasound treatment device for HIFU and ultrasound image, and control method therefor

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