JPH0947458A - Ultrasonic therapeupic device and applicator - Google Patents

Ultrasonic therapeupic device and applicator

Info

Publication number
JPH0947458A
JPH0947458A JP7203321A JP20332195A JPH0947458A JP H0947458 A JPH0947458 A JP H0947458A JP 7203321 A JP7203321 A JP 7203321A JP 20332195 A JP20332195 A JP 20332195A JP H0947458 A JPH0947458 A JP H0947458A
Authority
JP
Japan
Prior art keywords
ultrasonic
water bag
ultrasonic wave
applicator
formed
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
JP7203321A
Other languages
Japanese (ja)
Inventor
Katsuhiko Fujimoto
Mariko Shibata
真理子 柴田
克彦 藤本
Original Assignee
Toshiba Corp
株式会社東芝
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Toshiba Corp, 株式会社東芝 filed Critical Toshiba Corp
Priority to JP7203321A priority Critical patent/JPH0947458A/en
Publication of JPH0947458A publication Critical patent/JPH0947458A/en
Application status is Pending legal-status Critical

Links

Abstract

PROBLEM TO BE SOLVED: To prevent reduction in ultrasonic wave transmitting efficiency and leakage of a coupling liquid by a burst of a water bag film by forming a water bag into which an ultrasonic wave is introduced in a multilayer structure by interposing the coupling liquid between it and an ultrasonic wave generating source. SOLUTION: A water bag 5 to be removably installed in a packing material 6 of an applicator 1 by a ring 8, is formed in a multilayer structure by layering plural films. These films are made nonextensible-noncontractibe so as not to shut up bubbles inside like silicone rubber, and have heat resistance, and are higher in dynamic strength than silicone rubber in the same thickness, and do not hinder passing of an ultrasonic wave. For example, polyvinylidene chloride or the like is used. An O ring 7 to secure watertightness is sandwiched between the ring 8 and the packing material 6, and a coupling liquid 4 to introduce an ultrasonic wave generated by an ultrasonic wave generating source 2 into the body of an examine 3 without causing a loss, is sealed between the ultrasonic wave generating source 2 and the water bag 5.

Description

【発明の詳細な説明】 DETAILED DESCRIPTION OF THE INVENTION

【0001】 [0001]

【発明の属する技術分野】本発明は超音波を体内に照射して治療を行う超音波治療装置及びアプリケータに関する。 The present invention relates to relates to an ultrasonic therapy device and applicator for performing treatment by irradiating an ultrasonic wave into the body.

【0002】 [0002]

【従来の技術】近年、結石症の治療に体外から強力超音波パルスを断続的に照射し、無侵襲的に結石を破砕する結石破砕装置が実用化され、注目されている。 In recent years, intermittently irradiated with strong ultrasonic pulses from outside the treatment of lithiasis, non-invasively lithotriptor to crush the stone is commercialized, it is attracting attention. また、前立腺肥大症等の腫瘍に対し、比較的侵襲の少ない治療法として、体外から体内の患部に電磁波や超音波を照射することにより腫瘍を治療する温熱治療法(ハイパーサーミア)が施行されている。 Further, with respect to the tumor, such as prostate hyperplasia, as a relatively minimally invasive therapy, thermotherapy treatments for treating tumors (hyperthermia) are enforced by irradiating an electromagnetic wave or ultrasonic waves into the body of the affected part from outside the body . これは、腫瘍組織が正常組織よりも比較的熱に弱いことを利用して、患部を42.5 This takes advantage of the tumor tissue to be susceptible to relatively heat than normal tissue, 42.5 the affected area
℃以上に加温して腫瘍細胞だけを破壊する治療法である。 ℃ above warming is a therapy to destroy only the tumor cells. また、患部を60℃以上の高温にし、病理的組織に熱変性を起こさせる加熱治療が注目されるようになり、 Further, the affected area to a high temperature above 60 ° C., become heat treatment to cause thermal denaturation is noted pathological tissue,
特開昭61−013956号公報等に開示されているように、ピエゾ素子により体外で発生させた強力な超音波を体内の治療部位に集束させ、組織の超音波エネルギーの吸収による発熱で癌を加熱治療する装置が研究開発されている。 As disclosed in JP 61-013956 discloses such, focuses the strong ultrasonic wave generated in vitro by the piezoelectric element to the treatment site within the body, the cancer heat generated by the absorption of the tissue of the ultrasonic energy heating treatment devices have been research and development.

【0003】これら結石破砕装置及び超音波温熱治療装置は、超音波治療装置と総称される。 [0003] These lithotripsy and ultrasound hyperthermia treatment device are collectively referred to as ultrasound therapy apparatus. 超音波治療装置には、超音波発生源にピエゾ素子を用いる場合、消耗品がない、超音波強度を任意にコントロールできる、複数のピエゾ素子にかける駆動波形を位置制御することにより焦点位置をコントロールできる等の優れた長所がある(特開昭60−145131号公報、米国特許明細書第4526168号参照)。 The ultrasonic treatment apparatus, the case of using a piezoelectric element in the ultrasonic generating source, no consumables, the ultrasonic intensity can be arbitrarily controlled, controls the focus position by position control driving waveforms applied to the plurality of piezoelectric elements It has excellent advantages such as it (JP 60-145131, JP-see U.S. Pat. No. 4,526,168).

【0004】超音波治療装置はアプリケータを主要な構成要素としている。 [0004] The ultrasonic therapy device has an applicator as main components. アプリケータは、複数のピエゾ素子を球殻形状に配列してなる超音波発生源と、ピエゾ素子により発生した超音波を損失少なく生体内に導入せしめるために水袋膜にカップリング液を封入してなる水袋とから構成されている(特開昭60−145131号公報,特開平02−246961号公報参照)。 Applicator, sealed and ultrasonic transducer formed by arranging a plurality of piezoelectric elements in spherical shell shape, the coupling solution in water bag film to allowed to introduce into the body less loss ultrasonic waves generated by the piezoelectric element and a a water bag Te (JP 60-145131, JP-see JP Hei 02-246961). この水袋膜の材質としては、耐熱性と伸縮性が優れたシリコンゴムが多く用いられている。 This as the material of the water bag film, silicone rubber is often used to stretch and heat resistance superior.

【0005】 [0005]

【発明が解決しようとする課題】超音波治療装置では、 [SUMMARY OF THE INVENTION In ultrasonic therapy device,
ピエゾ素子を高電圧で駆動することにより発生する非常にエネルギーの高い強力超音波が用いられる。 Power ultrasonic is used very high energy generated by driving the piezoelectric element with high voltages. したがって、超音波の伝搬経路上に気泡や骨等の障害物があると、超音波がその部分で吸収・散乱され、発熱やキャビテーションを生じる。 Therefore, if there is an obstacle such as bubbles or bone on the propagation path of the ultrasonic wave, ultrasonic wave is absorbed and scattered by that portion, resulting in heat generation and cavitation. そこで、水袋膜と体表面との間のカップリングが問題となる。 Therefore, the coupling between the water bag film and the body surface is a problem. このカップリングには超音波ゼリーが用いられる。 Ultrasonic jelly is used in the coupling. つまり、水袋膜は超音波ゼリーを介して体表面に接触される。 That is, the water bag film may be in contact with a body surface through ultrasonic jelly. 仮に、超音波ゼリーに気泡が混入してしまうと、この気泡の部分で発熱する。 Assuming that the bubble to the ultrasonic jelly is thus mixed, to generate heat at portions of the bubble. この発熱により、水袋膜が損傷し、カップリング液が漏れたり、超音波経路にあたる膜の部分が変性してしまうと、超音波の伝搬効率が低下してしまうという不具合が生じる。 This heating, water bag film is damaged, or leakage of the coupling liquid, the film portion of the corresponding to the ultrasonic path will be modified, a problem that propagation efficiency of the ultrasonic wave is lowered occurs. この水袋膜の材料であるシリコンゴムでは、キャビテーションによる気泡がシリコンゴム中に侵入し、 The silicone rubber is a material the water bag film, bubbles due to cavitation penetrates into silicone rubber,
そのまま閉じこめられ、超音波の伝搬効率を著しく低下させてしまう。 Confined as it is, thus significantly reducing the ultrasonic wave propagation efficiency.

【0006】本発明の目的は、キャビテーション等による気泡が水袋膜中に閉じこめられて超音波の伝搬効率が低下することを防止でき、且つ水袋膜が破れて封入されているカップリング液体が漏れてしまうことがないような十分な力学的強度を確保でき、しかも、袋状に加工したり、凹凸のある体表面に密着できるようなある程度の柔軟性をも兼ね備える水袋膜を採用する超音波治療装置及びアプリケータを提供することである。 An object of the present invention can prevent the bubbles due to cavitation, etc. is lowered propagation efficiency of the ultrasonic wave is confined in the water bag film, it is and coupling liquid water bag film is sealed torn ultra that leaks can ensure a sufficient mechanical strength such that there is no, moreover, employs or processed into a bag shape, a water bag film also combines a certain degree of flexibility that allows close contact with the body surface having irregularities to provide an acoustic wave therapy apparatus and applicator.

【0007】 [0007]

【課題を解決するための手段】本発明は、超音波発生源で発生した超音波を、前記超音波発生源と水袋との間に封入したカップリング液を介して被検体内に導入せしめ、前記被検体内の患部を治療する超音波治療装置において、前記水袋は多層構造に形成されることを特徴とする。 Means for Solving the Problems The present invention, ultrasonic waves generated by the ultrasonic transducer, the allowed introduced via a coupling liquid encapsulated into the subject between the ultrasonic transducer and the water bag the in the ultrasonic treatment apparatus for treating an affected part in the subject, the water bag is being formed in a multilayer structure.

【0008】また、本発明は、被検体内の患部を治療するための超音波を発生する超音波発生源と、前記超音波発生源との間にカップリング液を封入し、前記超音波発生源で発生した前記超音波を前記カップリング液を介して前記被検体内に導入せしめるための水袋とを有するアプリケータにおいて、前記水袋は多層構造に形成されることを特徴とする。 Further, the present invention includes an ultrasonic source to generate ultrasonic waves to treat the affected area of ​​the subject, the sealed coupling solution between the ultrasonic transducer, the ultrasonic generator in the applicator and a water bag for the ultrasonic waves generated by the source through the coupling solution allowed to introduce into the inside of the subject, the water bag is being formed in a multilayer structure.

【0009】水袋を多層構造で形成することにより、水袋を単層膜として同じ材料、同じ厚さで形成するよりも、柔軟性が高くなる。 [0009] By forming the water bag with a multilayer structure, the same material the water bag as a single layer film, rather than formed in the same thickness, flexibility is increased. これにより、湾曲しやすく、袋状に加工することが容易になり、また患者の体表に対する密着性が向上する。 Thereby, easily bent, it becomes easy to be processed into a bag shape, also improves adhesion to the body surface of the patient. また、キャビテーションや熱の影響で膜が損傷を受ける場合でも、単層膜であれば材料中に気泡を閉じこめてしまったり、薄ければ破れてカップリング液が漏れてしまったりするが、本発明のように水袋が多層構造であれば1枚破れて、気泡が残留しない。 Further, even if the film under the influence of cavitation and heat damage, or worse trapped air bubbles into the material if it is a single-layer film, but or leaked the coupling solution torn if thin, the present invention Mizubukuro is torn one if a multilayer structure as described above, air bubbles do not remain.
また、水袋が多層構造であれば、破損が各層で止まり、 In addition, if the water bag is a multi-layer structure, corruption stops at each layer,
全ての層に波及し難いので、完全に破れてカップリング液が漏れる可能性は低下される。 Since hardly spread to all layers, possibly coupling solution leaks completely tear is reduced.

【0010】 [0010]

【発明の実施の形態】以下に本発明の実施の形態について図面を参照して説明する。 DETAILED DESCRIPTION OF THE INVENTION be described with reference to the drawings, embodiments of the present invention are described below. 図1に一実施の形態による超音波治療装置の構成、図2に図1のアプリケータの断面構造を示す。 Arrangement of an ultrasonic therapeutic apparatus according to the embodiment in FIG. 1 shows a cross-sectional structure of the applicator of Figure 1 Figure 2. 治療用超音波を発生し、生体内に導入するためのアプリケータ1は、複数のピエゾ素子が球殻形状に配列された超音波発生源2を有する。 The therapeutic ultrasound occurs, the applicator 1 for introduction into a living body, having an ultrasonic source 2 in which a plurality of piezoelectric elements arranged in a spherical shell shape. 各ピエゾ素子から発生した超音波は、焦点10に集束する。 Ultrasonic waves generated from the piezoelectric element is focused on the focal point 10. 焦点10 Focus 10
は、球殻形状の曲率に応じて幾何学的に定まる。 It is determined geometrically in accordance with the curvature of the spherical shell shape. 超音波発生源2はバッキング材6に固定されている。 Ultrasonic transducer 2 is fixed to the backing material 6. バッキング材6は、空気バッキングまたはピエゾ素子の冷却を促進する構造を有する。 The backing material 6 has a structure that promotes cooling of air backing or piezoelectric element. 水袋5は、リング8によりバッキング材6に取り外し可能な状態で取り付けられる。 Water bag 5 is mounted in a removably to the backing material 6 by a ring 8. リング8とバッキング材6との間には、水密を取るためのO Between the ring 8 and the backing material 6, O for taking watertight
リング7が挟み込まれている。 Ring 7 is sandwiched. 超音波発生源2と水袋5 Ultrasonic source 2 and the water bag 5
との間には、超音波発生源2で発生した超音波を損失少なく被検体3内に導入せしめるためのカップリング液4 And between the ultrasonic source 2 coupling for allowing introduction of the ultrasonic waves generated in the loss less subject 3 with liquid 4
が封入される。 There is enclosed.

【0011】駆動回路12は、超音波を一斉に発生させるために、超音波発生源2の複数のピエゾ素子を駆動する。 [0011] The drive circuit 12 in order to generate simultaneously the ultrasonic, driving a plurality of piezoelectric elements of the ultrasonic source 2. アプリケータ1は、メカニカルアーム14により移動可能に支持される。 The applicator 1 is supported movably by the mechanical arm 14. アプリケータ1の移動は、制御回路13の制御により電動で、又は手動で行われる。 Movement of the applicator 1, the electric by, or performed manually by the control of the control circuit 13.

【0012】超音波発生源2の中央部には挿入孔16が開けられ、ここに超音波プローブ15が焦点10に近付く/離れることができるようにスライド可能に、及び回動可能に挿入される。 [0012] insertion hole 16 in the center portion of the ultrasonic transducer 2 is opened, wherein the ultrasonic probe 15 is slidably and inserted rotatably as to be able to approach / leaving the focal point 10 . 超音波プローブ15のスライド及び回動運動は、プローブ位置制御回路17により制御される。 Slide and pivotal movement of the ultrasonic probe 15 is controlled by a probe position control circuit 17. 超音波診断装置18は焦点10の付近の超音波画像を得るために超音波プローブ15を駆動する。 The ultrasonic diagnostic apparatus 18 for driving the ultrasonic probe 15 in order to obtain an ultrasound image of the vicinity of the focal point 10.

【0013】超音波診断装置18は、図示しないが、C [0013] The ultrasonic diagnostic apparatus 18, although not shown, C
PUをシステム全体の制御中枢として次のように構成されている。 It is constructed as follows the PU as a control center of the whole system. 超音波プローブ15には超音波送信部と超音波受信部とが接続される。 The ultrasonic probe 15 is connected to the ultrasonic wave transmitter and the ultrasonic receiver. 超音波送信部は、パルス発生器、送信遅延回路、パルサとを有する。 Ultrasonic wave transmitter comprises a pulse generator, a transmission delay circuit, and a pulser. パルス発生器は例えば5KHzのレート周波数fr (周期;1/fr) Pulse generator for example 5KHz rate frequency fr (period; 1 / fr)
でレートパルスを繰り返し発生する。 In repeatedly generates a rate pulse. このレートパルスはチャンネル数に分配され、送信遅延回路に送られる。 The rate pulses are distributed to the number of channels, it is sent to the transmission delay circuit.
送信遅延回路は、超音波をビーム状に集束し且つ送信指向性を決定するのに必要な遅延時間を各レートパルスに与える。 Transmission delay circuit gives a delay time necessary for determining a focused and transmission directivity of the ultrasonic beam shape to each rate pulse. パルサは、送信遅延回路からレートパルスを受けたタイミングでプローブ15にチャンネル毎に電圧パルスを印加する。 Pulser applies a voltage pulse to each channel in the probe 15 at the timing of receiving the rate pulse from the transmission delay circuit. これにより超音波ビームが被検体に送信される。 Thereby the ultrasonic beam is transmitted to the object. 被検体内の音響インピーダンスの不連続面で反射した反射波はプローブ15を介して超音波受信部で受信される。 Reflected wave reflected by a discontinuity surface of acoustic impedance of the subject are received by the ultrasonic receiver through the probe 15. 超音波受信部は、プリアンプ、受信遅延回路、加算器を有する。 Ultrasonic receiver includes a preamplifier, a reception delay circuit, an adder. 受信信号は、チャンネル毎にプリアンプで増幅され、受信遅延回路により受信指向性を決定するのに必要な遅延時間を与えられ、加算器で加算される。 The received signal is amplified by a preamplifier for each channel, given a delay time required to determine reception directivity by the reception delay circuit, it is added by the adder. この加算により送信指向性及び受信指向性に応じた方向からの反射成分が強調されたエコー信号が得られる。 Echo signals reflected component is emphasized from a direction corresponding to the transmission directivity and reception directivity by the addition can be obtained. エコー信号は、レシーバ部に送られる。 Echo signal is sent to the receiver unit. レシーバ部は、対数増幅器、包絡線検波回路、アナログディジタルコンバータ(A/D)から構成される。 The receiver unit is a logarithmic amplifier, an envelope detection circuit, and an analog digital converter (A / D). 対数増幅器は、 Logarithmic amplifier,
エコー信号を対数増幅する。 The echo signal to logarithmic amplification. 包絡線検波回路は対数増幅器からの出力信号の包絡線を検波する。 Envelope detection circuit for detecting the envelope of the output signal from the logarithmic amplifier. この検波信号はアナログディジタルコンバータを介してディジタル化され、Bモード画像データとして出力される。 The detected signal is digitized via an analog-to-digital converter is output as B-mode image data. このBモード画像データは、ディジタルスキャンコンバータ(DS The B-mode image data, a digital scan converter (DS
C)を介して表示部に送られ、Bモード画像としてビジュアルに濃淡表示される。 Is sent to the display unit via a C), is gray displayed visually as a B-mode image.

【0014】オペレータはこのBモード画像を見ながら腫瘍等の患部11の位置を確認し、焦点10を患部11 [0014] The operator confirms the position of the affected part 11 of the tumor or the like while viewing the B-mode image, the focus 10 affected area 11
に位置合わせしたり、治療計画を立てたり、治療中に治療の進行を確認することすることができるようになっている。 Or aligned with, or make a treatment plan, so that it can be possible to confirm the treatment progress of during treatment. 患部11に焦点10を位置合わせした後、超音波発生源2を駆動して超音波を発生せしめ、焦点10に存在する患部11を治療する。 After aligning the focal point 10 to the affected area 11, by driving the ultrasonic transducer 2 and by which the ultrasonic waves to treat the affected area 11 that exists in the focal 10.

【0015】なお、治療の際には、治療台19の上に固定された患者3に対してアプリケータ1をセッティングし、水袋5を超音波ゼリー9により患者3の体表面に密着させる。 [0015] At the time of treatment, and setting the applicator 1 for patients 3 fixed on the treatment table 19, a water bag 5 by ultrasonic jelly 9 is brought into close contact with the body surface of the patient 3.

【0016】図3は水袋5の断面構造を示す。 [0016] Figure 3 shows a cross-sectional structure of Mizubukuro 5. 従来では、図3(a)に示すように、水袋は、シリコンゴム等の厚さ0.01mm程度の単層膜で形成されていた。 Conventionally, as shown in FIG. 3 (a), the water bag was formed of a single layer film having a thickness of about 0.01mm such as silicone rubber. これに対して、本発明では、図3(b)に示すように、水袋5は、複数枚のフィルムが積層された多層構造で形成される。 In contrast, in the present invention, as shown in FIG. 3 (b), water bag 5 is formed in a multilayer structure in which a plurality of films are laminated. フィルムの材料としては、シリコンゴムのように中に気泡を閉じ込めることのないように、非伸縮性で耐熱性があり、同じ厚さでは力学的強度がシリコンゴムより高く、且つ超音波の通過を妨げないような、例えばポリ塩化ビニリデン(PVDC)、PVC(ポリ塩化ビニル)、LDPE(低密度ポリエチレン)、L−LDP As the material of the film, so as not to confine bubbles in as silicone rubber, has heat resistance non-stretchable, high mechanical strength of silicon rubber at the same thickness, and ultrasound to pass hindered not like, for example, polyvinylidene chloride (PVDC), PVC (polyvinyl chloride), LDPE (low density polyethylene), L-LDP
E(リニヤー低密度ポリエチレン)、HDPE(高密度ポリエチレン)等の塩化樹脂材料の各共重合体のフィルム、又はポリテトラフルオロエチレン(PTFE)等のフッ素樹脂のフィルムが採用される。 E (Riniya low density polyethylene), HDPE films of copolymers chloride resin material (high density polyethylene) or the like, or a film of polytetrafluoroethylene (PTFE) such as a fluorine resin is employed. この種のフィルムは伸縮性が無く、また硬質であるため、袋状に加工したり、凹凸のある体表面に密着できるように、ある程度の柔軟性を獲得するためには、例えば0.01mm程度の薄さにする必要がある。 Film of this type is not stretchable, also because it is hard, or processed into a bag shape so as to be in close contact with the body surface having irregularities, in order to obtain a certain degree of flexibility, for example, 0.01mm of about it is necessary to thin. しかし、この種のフィルムを薄く形成すると、力学的強度が保てず、破れて封入されているカップリング液体が漏れてしまうおそれがあるため、本発明のごとく多層構造とすることが特に有効である。 However, when thinner this kind of film, mechanical strength can not be maintained, there is a risk that the coupling liquid is enclosed torn leaks, it is particularly effective to a multi-layer structure as in the present invention is there. さらに、透明度の高い材料をフィルムに採用することにより、カップリング液中の気泡や不純物の存在を発見しやすくなるという効果が得られる。 Further, by adopting a material having high transparency to the film, the effect is obtained that it becomes easier to discover the presence of bubbles and impurities of the coupling liquid. なお、上記材料のフィルムは、伸縮性がないため、シリコンゴムのように膨らませて用いることができないものもあるため、図4に示すような蛇腹23の装置に用いることにより、カップリング液4の量の増減により患部11に対する超音波発生源2の距離を調整するようにすることが好ましい。 The film of the material, since there is no stretch, because there may not be used inflatable as silicone rubber, by using the apparatus of the bellows 23 as shown in FIG. 4, the coupling solution 4 it is preferable to adjust the distance of the ultrasonic transducer 2 for the affected area 11 by the amount of increase or decrease. なお、蛇腹は別途も受けてもよいし、フィルム自体を蛇腹状に形成してもよい。 Incidentally, the bellows may be separately also received, may be formed film itself in a bellows.

【0017】水袋5の多層構造を構成する複数枚のフィルムは、超音波の通過を妨げたり、キャビテーション発生の原因となる気泡が閉じ込められることのないように、真空状態で密着される。 The plurality of films constituting the multilayer structure of the water bag 5, or impede the passage of ultrasonic, so as not to have bubbles cause cavitation trapped, into close contact in a vacuum state. なお、フィルム間に閉じ込められた気泡を追い出すために、図3(e)に斜線で示すように、脱気された液体、例えば脱気水をフィルム間に充填することは、歩留まりの向上の観点から好ましい。 Incidentally, in view of to expel air bubbles trapped between the film, as indicated by hatching in FIG. 3 (e), degassed liquid, for example, filling the degassed water between the film, the improvement in yield preferable from. また、脱気水の代わりに、粘性がある液体をフィルム間に充填することは、キャビテーションの発生を抑制できる観点からさらに好ましい。 Instead of degassed water, filling the liquid has viscosity between film further preferable from the viewpoint of suppressing the occurrence of cavitation. 粘性がある液体としては、例えば超音波ゼリーのようなゲル状の物質が採用される。 The liquid is viscous, such as a gel-like substance such as ultrasound jelly are employed. 勿論、脱気された液体や粘性がある液体としては、無害であることが最低条件とされる。 Of course, as the liquid is deaerated liquid or viscous, it is the minimum condition is harmless. また、図3 In addition, FIG. 3
(f)に示すように、局部的に脱気された液体や粘性がある液体をフィルム間に充填させて、水袋5を丸みを帯びた形状に加工するようにしてもよい。 (F), the liquid that locally there is degassed liquid or viscous is filled between the film may be processed with water bag 5 in a rounded shape.

【0018】水袋5を構成する各層(各フィルム)の厚さ、または水袋5の全体の厚さは、超音波の散乱を抑制し、患部に到達するまでのエネルギー損失を抑えるために、治療用超音波の波長λに応じて、λ/2以下に形成される。 [0018] Each layer constituting the water bag 5 (each film) thickness or the total thickness of the Mizubukuro 5 suppresses the scattering of ultrasound, in order to reduce energy loss to reach the affected area, depending on the wavelength lambda of the therapeutic ultrasound, it is formed on the lambda / 2 or less. 例えば、1枚のフィルムは0.01mm程度の厚さを有する。 For example, a sheet of film has a thickness of about 0.01 mm. この場合、水袋5は、5枚のフィルムが積層された多層構造に形成され、全体の厚さとしては0.05mmの厚さを有する。 In this case, the water bag 5 is formed in a multilayer structure in which five films are stacked, the overall thickness has a thickness of 0.05 mm.

【0019】このように水袋5を複数枚のフィルムで多層構造に形成することにより、水袋5を単層膜として同じ材料、同じ厚さで形成するよりも、柔軟性が高くなる。 [0019] By thus forming the Mizubukuro 5 a multilayer structure with a plurality of films, the same material the water bag 5 as a single layer film, rather than formed in the same thickness, flexibility is increased. これにより、湾曲しやすく、袋状に加工することが容易になり、また患者の体表に対する密着性が向上する。 Thereby, easily bent, it becomes easy to be processed into a bag shape, also improves adhesion to the body surface of the patient. また、キャビテーションや熱の影響で膜が損傷を受ける場合でも、単層膜であれば図3(c)に示すよう材料中に気泡を閉じこめてしまったり、薄ければ破れてカップリング液4が漏れてしまったりするが、本発明のように水袋5が多層構造であれば図3(d)に示すように1枚破れて、気泡が残留しない。 Further, even if the film under the influence of cavitation and heat damage, if a single layer film or worse trapped air bubbles in a material as shown in FIG. 3 (c), the coupling liquid 4 is broken if thin or leaked, but Mizubukuro 5 as in the present invention is torn one as shown in FIG. 3 (d) if a multilayer structure, no air bubbles remain. また、水袋5が多層構造であれば、破損が各フィルムで止まり、全てのフィルムに波及し難いので、完全に破れてカップリング液が漏れる可能性は低下される。 Further, if water bag 5 is a multi-layer structure, breakage will stop in the film, since it is difficult to spread to all film, the possibility of coupling fluid leakage completely torn is reduced.

【0020】なお、図5に示すように、超音波発生源2'を構成する複数のピエゾ素子が平面的に配列され遅延制御により任意の深さに焦点10を形成することができる場合、筒状のカップリング液容器24を用いてもよい。 [0020] When the can as shown in FIG. 5, a plurality of piezoelectric elements constituting the ultrasonic source 2 'forms a focus 10 at any depth by planarly arrayed delay control, cylinder it may be used Jo coupling fluid container 24. 図5に示すように、フェーズドアレイ型超音波発生源2'は、バッキング材6'に固定されている。 As shown in FIG. 5, a phased array type ultrasonic transducer 2 ', backing material 6' is fixed to. バッキング材6'には、取り外し可能なカップリング液容器2 The backing material 6 ', detachable coupling fluid container 2
4が取り付けられている。 4 which it is attached. 更に、カップリング容器24 Furthermore, coupling the container 24
の開口部25には水袋5'がリング8により取り付けられている。 The openings 25 Mizubukuro 5 'is mounted by the ring 8. 水袋5'とカップリング液容器24'との間にはOリング7が挟まれていて、水密を取っている。 O-ring 7 is provided between the water bag 5 'and the coupling fluid container 24' and is not sandwiched, it is taking watertight. カップリング容器24はバッキング6'にはめ込み式になっていて、患部の深さに合わせて高さの異なる容器を用いてもよい。 Coupling the container 24 have become telescopically backing 6 ', may use different containers together height to the depth of the affected part. カップリング液4の出し入れは、例えば図5に示すように、バッキング材6'に設けられた注入孔26と排出孔27により行う。 Out of the coupling liquid 4, for example, as shown in FIG. 5 performs the injection hole 26 provided in the backing material 6 'by the discharge hole 27.

【0021】なお本発明は上述した実施の形態に限定されること無く、種々変形して実施可能である。 [0021] Note that the present invention is not limited to the embodiments described above can be implemented in various modifications. 本発明は、結石破砕装置、温熱治療装置、加熱治療装置等の種々の超音波治療装置に適用可能である。 The present invention, lithotripsy, the thermal treatment device is applicable to various ultrasonic treatment apparatus such as a thermal treatment apparatus.

【0022】 [0022]

【発明の効果】本発明は、超音波発生源で発生した超音波を、前記超音波発生源と水袋との間に封入したカップリング液を介して被検体内に導入せしめ、前記被検体内の患部を治療する超音波治療装置において、前記水袋は多層構造に形成されることを特徴とする。 According to the present invention, the ultrasonic waves generated by the ultrasonic source, the allowed introduced via a coupling liquid encapsulated into the subject between the ultrasonic transducer and the water bag, the subject in ultrasonic therapy apparatus for treating an affected part of the inner, the water bag is being formed in a multilayer structure.

【0023】また、本発明は、被検体内の患部を治療するための超音波を発生する超音波発生源と、前記超音波発生源との間にカップリング液を封入し、前記超音波発生源で発生した前記超音波を前記カップリング液を介して前記被検体内に導入せしめるための水袋とを有するアプリケータにおいて、前記水袋は多層構造に形成されることを特徴とする。 Further, the present invention encapsulates the ultrasonic transducer to generate ultrasonic waves to treat the affected part in the subject, the coupling solution between the ultrasonic transducer, the ultrasonic generator in the applicator and a water bag for the ultrasonic waves generated by the source through the coupling solution allowed to introduce into the inside of the subject, the water bag is being formed in a multilayer structure.

【0024】水袋を多層構造で形成することにより、水袋を単層膜として同じ材料、同じ厚さで形成するよりも、柔軟性が高くなる。 [0024] By forming the water bag with a multilayer structure, the same material the water bag as a single layer film, rather than formed in the same thickness, flexibility is increased. これにより、湾曲しやすく、袋状に加工することが容易になり、また患者の体表に対する密着性が向上する。 Thereby, easily bent, it becomes easy to be processed into a bag shape, also improves adhesion to the body surface of the patient. また、キャビテーションや熱の影響で膜が損傷を受ける場合でも、単層膜であれば材料中に気泡を閉じこめてしまったり、薄ければ破れてカップリング液が漏れてしまったりするが、本発明のように水袋が多層構造であれば1枚破れて、気泡が残留しない。 Further, even if the film under the influence of cavitation and heat damage, or worse trapped air bubbles into the material if it is a single-layer film, but or leaked the coupling solution torn if thin, the present invention Mizubukuro is torn one if a multilayer structure as described above, air bubbles do not remain.
また、水袋が多層構造であれば、破損が各層で止まり、 In addition, if the water bag is a multi-layer structure, corruption stops at each layer,
全ての層に波及し難いので、完全に破れてカップリング液が漏れる可能性は低下される。 Since hardly spread to all layers, possibly coupling solution leaks completely tear is reduced.

【図面の簡単な説明】 BRIEF DESCRIPTION OF THE DRAWINGS

【図1】本発明の一実施の形態による超音波治療装置の構成図。 Figure 1 is a configuration diagram of an ultrasonic therapeutic apparatus according to an embodiment of the present invention.

【図2】図1のアプリケータの断面構造図。 FIG. 2 is a cross-sectional structure view of the applicator of FIG. 1.

【図3】図2の水袋の断面構造及び効果説明図。 FIG. 3 is a cross-sectional structure and effect showing a water bag of FIG.

【図4】蛇腹構造に形成された水袋を有するアプリケータの断面構造図。 FIG. 4 is a cross-sectional structural view of an applicator having a water bag which is formed on the bellows structure.

【図5】カップリング液容器を採用するアプリケータの断面構造図 FIG. 5 is a cross-sectional structural view of an applicator employing a coupling liquid container

【符号の説明】 DESCRIPTION OF SYMBOLS

1…アプリケータ、 2…超音波発生源、 3…被検体、 4…カップリング液、 5…水袋、 6…バッキング材、 7…Oリング、 8…リング、 9…超音波ゼリー、 10…焦点、 11…患部、 12…駆動回路、 13…制御回路、 14…メカニカルアーム、 15…超音波プローブ、 16…プローブ挿入孔、 17…プローブ位置制御回路、 18…超音波診断装置、 19…治療台。 1 ... applicator 2 ... ultrasonic transducer, 3 ... subject, 4 ... coupling solution, 5 ... water bag, 6 ... backing material, 7 ... O-ring, 8 ... ring, 9 ... ultrasonic jelly, 10 ... focus, 11 ... affected area, 12 ... drive circuit, 13 ... control circuit, 14 ... mechanical arm, 15 ... ultrasonic probe, 16 ... probe insertion hole, 17 ... probe position control circuit, 18 ... ultrasonic diagnostic apparatus, 19 ... treatment table.

Claims (8)

    【特許請求の範囲】 [The claims]
  1. 【請求項1】超音波発生源で発生した超音波を、前記超音波発生源と水袋との間に封入したカップリング液を介して被検体内に導入せしめ、前記被検体内の患部を治療する超音波治療装置において、 前記水袋は多層構造に形成されることを特徴とする超音波治療装置。 The method according to claim 1] ultrasonic waves generated by the ultrasonic transducer, through said coupling solution was enclosed between the ultrasonic transducer and the water bag allowed introduced into a subject, the affected part in the subject in ultrasonic therapy device for treating, ultrasonic therapy system the water bag is being formed in a multilayer structure.
  2. 【請求項2】前記水袋は各層の厚さが、前記超音波の波長をλとして、λ/2以下に形成されることを特徴とする請求項1記載の超音波治療装置。 Wherein the thickness of the water bag each layer, the as the wavelength of the ultrasonic wave lambda, lambda / 2 ultrasonic therapeutic apparatus according to claim 1, characterized in that it is formed as follows.
  3. 【請求項3】前記水袋は非伸縮性材料で形成されていることを特徴とする請求項1記載の超音波治療装置。 3. The ultrasonic treatment apparatus according to claim 1, wherein the water bag which is formed of a non-stretchable material.
  4. 【請求項4】前記水袋は層間に脱気された液体が充填されることを特徴とする請求項1記載の超音波治療装置。 Wherein said water bag ultrasonic therapeutic apparatus according to claim 1, characterized in that the liquid is degassed interlayer is filled.
  5. 【請求項5】被検体内の患部を治療するための超音波を発生する超音波発生源と、 前記超音波発生源との間にカップリング液を封入し、前記超音波発生源で発生した前記超音波を前記カップリング液を介して前記被検体内に導入せしめるための水袋とを有するアプリケータにおいて、 前記水袋は多層構造に形成されることを特徴とするアプリケータ。 5. A ultrasonic transducer for generating ultrasonic waves to treat the affected area of ​​the subject, the sealed coupling solution between the ultrasonic transducer, generated by the ultrasonic transducer applicator, characterized in that said at applicator and a water bag for allowing introduction of ultrasound into the inside of the subject through the coupling solution, the water bag is formed in a multilayer structure.
  6. 【請求項6】前記水袋は各層の厚さが、前記超音波の波長をλとして、λ/2以下に形成されることを特徴とする請求項5記載のアプリケータ。 6. A thickness of the water bag each layer, the as the wavelength of the ultrasonic wave lambda, applicator according to claim 5, characterized in that it is formed into lambda / 2 or less.
  7. 【請求項7】前記水袋は非伸縮性材料で形成されていることを特徴とする請求項5記載のアプリケータ。 7. The applicator of claim 5, wherein the water bag which is formed of a non-stretchable material.
  8. 【請求項8】前記水袋は層間に脱気された液体が充填されることを特徴とする請求項5記載のアプリケータ。 8. The applicator of claim 5, wherein the water bag, wherein a liquid is degassed interlayer is filled.
JP7203321A 1995-08-09 1995-08-09 Ultrasonic therapeupic device and applicator Pending JPH0947458A (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP7203321A JPH0947458A (en) 1995-08-09 1995-08-09 Ultrasonic therapeupic device and applicator

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
JP7203321A JPH0947458A (en) 1995-08-09 1995-08-09 Ultrasonic therapeupic device and applicator

Publications (1)

Publication Number Publication Date
JPH0947458A true JPH0947458A (en) 1997-02-18

Family

ID=16472090

Family Applications (1)

Application Number Title Priority Date Filing Date
JP7203321A Pending JPH0947458A (en) 1995-08-09 1995-08-09 Ultrasonic therapeupic device and applicator

Country Status (1)

Country Link
JP (1) JPH0947458A (en)

Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2010527644A (en) * 2007-05-07 2010-08-19 ガイデッド セラピー システムズ, エル.エル.シー. Method and system for combining the acoustic energy using a coupler member, and collected at the focal
US8690780B2 (en) 2004-10-06 2014-04-08 Guided Therapy Systems, Llc Noninvasive tissue tightening for cosmetic effects
US8690778B2 (en) 2004-10-06 2014-04-08 Guided Therapy Systems, Llc Energy-based tissue tightening
US8858471B2 (en) 2011-07-10 2014-10-14 Guided Therapy Systems, Llc Methods and systems for ultrasound treatment
US8857438B2 (en) 2010-11-08 2014-10-14 Ulthera, Inc. Devices and methods for acoustic shielding
US8868958B2 (en) 2005-04-25 2014-10-21 Ardent Sound, Inc Method and system for enhancing computer peripheral safety
US8915853B2 (en) 2004-10-06 2014-12-23 Guided Therapy Systems, Llc Methods for face and neck lifts
US8915870B2 (en) 2004-10-06 2014-12-23 Guided Therapy Systems, Llc Method and system for treating stretch marks
US8915854B2 (en) 2004-10-06 2014-12-23 Guided Therapy Systems, Llc Method for fat and cellulite reduction
US8920324B2 (en) 2004-10-06 2014-12-30 Guided Therapy Systems, Llc Energy based fat reduction
US8926533B2 (en) 2003-12-30 2015-01-06 Liposonix, Inc. Therapy head for use with an ultrasound system
US8932224B2 (en) 2004-10-06 2015-01-13 Guided Therapy Systems, Llc Energy based hyperhidrosis treatment
US9011336B2 (en) 2004-09-16 2015-04-21 Guided Therapy Systems, Llc Method and system for combined energy therapy profile
US9011337B2 (en) 2011-07-11 2015-04-21 Guided Therapy Systems, Llc Systems and methods for monitoring and controlling ultrasound power output and stability
US9039617B2 (en) 2009-11-24 2015-05-26 Guided Therapy Systems, Llc Methods and systems for generating thermal bubbles for improved ultrasound imaging and therapy
US9114247B2 (en) 2004-09-16 2015-08-25 Guided Therapy Systems, Llc Method and system for ultrasound treatment with a multi-directional transducer
US9149658B2 (en) 2010-08-02 2015-10-06 Guided Therapy Systems, Llc Systems and methods for ultrasound treatment
US9216276B2 (en) 2007-05-07 2015-12-22 Guided Therapy Systems, Llc Methods and systems for modulating medicants using acoustic energy
US9263663B2 (en) 2012-04-13 2016-02-16 Ardent Sound, Inc. Method of making thick film transducer arrays
US9272162B2 (en) 1997-10-14 2016-03-01 Guided Therapy Systems, Llc Imaging, therapy, and temperature monitoring ultrasonic method
US9320537B2 (en) 2004-10-06 2016-04-26 Guided Therapy Systems, Llc Methods for noninvasive skin tightening
US9504446B2 (en) 2010-08-02 2016-11-29 Guided Therapy Systems, Llc Systems and methods for coupling an ultrasound source to tissue
US9510802B2 (en) 2012-09-21 2016-12-06 Guided Therapy Systems, Llc Reflective ultrasound technology for dermatological treatments
US9566454B2 (en) 2006-09-18 2017-02-14 Guided Therapy Systems, Llc Method and sysem for non-ablative acne treatment and prevention
US9694212B2 (en) 2004-10-06 2017-07-04 Guided Therapy Systems, Llc Method and system for ultrasound treatment of skin
US9700340B2 (en) 2004-10-06 2017-07-11 Guided Therapy Systems, Llc System and method for ultra-high frequency ultrasound treatment
US9827449B2 (en) 2004-10-06 2017-11-28 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US9907535B2 (en) 2000-12-28 2018-03-06 Ardent Sound, Inc. Visual imaging system for ultrasonic probe
US10039938B2 (en) 2004-09-16 2018-08-07 Guided Therapy Systems, Llc System and method for variable depth ultrasound treatment

Cited By (63)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9272162B2 (en) 1997-10-14 2016-03-01 Guided Therapy Systems, Llc Imaging, therapy, and temperature monitoring ultrasonic method
US9907535B2 (en) 2000-12-28 2018-03-06 Ardent Sound, Inc. Visual imaging system for ultrasonic probe
US8926533B2 (en) 2003-12-30 2015-01-06 Liposonix, Inc. Therapy head for use with an ultrasound system
US9011336B2 (en) 2004-09-16 2015-04-21 Guided Therapy Systems, Llc Method and system for combined energy therapy profile
US10039938B2 (en) 2004-09-16 2018-08-07 Guided Therapy Systems, Llc System and method for variable depth ultrasound treatment
US9114247B2 (en) 2004-09-16 2015-08-25 Guided Therapy Systems, Llc Method and system for ultrasound treatment with a multi-directional transducer
US9895560B2 (en) 2004-09-24 2018-02-20 Guided Therapy Systems, Llc Methods for rejuvenating skin by heating tissue for cosmetic treatment of the face and body
US9095697B2 (en) 2004-09-24 2015-08-04 Guided Therapy Systems, Llc Methods for preheating tissue for cosmetic treatment of the face and body
US10328289B2 (en) 2004-09-24 2019-06-25 Guided Therapy Systems, Llc Rejuvenating skin by heating tissue for cosmetic treatment of the face and body
US9833640B2 (en) 2004-10-06 2017-12-05 Guided Therapy Systems, L.L.C. Method and system for ultrasound treatment of skin
US8920324B2 (en) 2004-10-06 2014-12-30 Guided Therapy Systems, Llc Energy based fat reduction
US8915854B2 (en) 2004-10-06 2014-12-23 Guided Therapy Systems, Llc Method for fat and cellulite reduction
US8932224B2 (en) 2004-10-06 2015-01-13 Guided Therapy Systems, Llc Energy based hyperhidrosis treatment
US8915870B2 (en) 2004-10-06 2014-12-23 Guided Therapy Systems, Llc Method and system for treating stretch marks
US10238894B2 (en) 2004-10-06 2019-03-26 Guided Therapy Systems, L.L.C. Energy based fat reduction
US9039619B2 (en) 2004-10-06 2015-05-26 Guided Therapy Systems, L.L.C. Methods for treating skin laxity
US10046181B2 (en) 2004-10-06 2018-08-14 Guided Therapy Systems, Llc Energy based hyperhidrosis treatment
US8915853B2 (en) 2004-10-06 2014-12-23 Guided Therapy Systems, Llc Methods for face and neck lifts
US10245450B2 (en) 2004-10-06 2019-04-02 Guided Therapy Systems, Llc Ultrasound probe for fat and cellulite reduction
US10252086B2 (en) 2004-10-06 2019-04-09 Guided Therapy Systems, Llc Ultrasound probe for treatment of skin
US10265550B2 (en) 2004-10-06 2019-04-23 Guided Therapy Systems, L.L.C. Ultrasound probe for treating skin laxity
US10010721B2 (en) 2004-10-06 2018-07-03 Guided Therapy Systems, L.L.C. Energy based fat reduction
US8690779B2 (en) 2004-10-06 2014-04-08 Guided Therapy Systems, Llc Noninvasive aesthetic treatment for tightening tissue
US9283410B2 (en) 2004-10-06 2016-03-15 Guided Therapy Systems, L.L.C. System and method for fat and cellulite reduction
US9283409B2 (en) 2004-10-06 2016-03-15 Guided Therapy Systems, Llc Energy based fat reduction
US9320537B2 (en) 2004-10-06 2016-04-26 Guided Therapy Systems, Llc Methods for noninvasive skin tightening
US10010725B2 (en) 2004-10-06 2018-07-03 Guided Therapy Systems, Llc Ultrasound probe for fat and cellulite reduction
US9421029B2 (en) 2004-10-06 2016-08-23 Guided Therapy Systems, Llc Energy based hyperhidrosis treatment
US9427600B2 (en) 2004-10-06 2016-08-30 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US9427601B2 (en) 2004-10-06 2016-08-30 Guided Therapy Systems, Llc Methods for face and neck lifts
US9440096B2 (en) 2004-10-06 2016-09-13 Guided Therapy Systems, Llc Method and system for treating stretch marks
US8690778B2 (en) 2004-10-06 2014-04-08 Guided Therapy Systems, Llc Energy-based tissue tightening
US10010724B2 (en) 2004-10-06 2018-07-03 Guided Therapy Systems, L.L.C. Ultrasound probe for treating skin laxity
US10010726B2 (en) 2004-10-06 2018-07-03 Guided Therapy Systems, Llc Ultrasound probe for treatment of skin
US9522290B2 (en) 2004-10-06 2016-12-20 Guided Therapy Systems, Llc System and method for fat and cellulite reduction
US9533175B2 (en) 2004-10-06 2017-01-03 Guided Therapy Systems, Llc Energy based fat reduction
US9974982B2 (en) 2004-10-06 2018-05-22 Guided Therapy Systems, Llc System and method for noninvasive skin tightening
US9694211B2 (en) 2004-10-06 2017-07-04 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US10046182B2 (en) 2004-10-06 2018-08-14 Guided Therapy Systems, Llc Methods for face and neck lifts
US9700340B2 (en) 2004-10-06 2017-07-11 Guided Therapy Systems, Llc System and method for ultra-high frequency ultrasound treatment
US9707412B2 (en) 2004-10-06 2017-07-18 Guided Therapy Systems, Llc System and method for fat and cellulite reduction
US9713731B2 (en) 2004-10-06 2017-07-25 Guided Therapy Systems, Llc Energy based fat reduction
US8690780B2 (en) 2004-10-06 2014-04-08 Guided Therapy Systems, Llc Noninvasive tissue tightening for cosmetic effects
US9827450B2 (en) 2004-10-06 2017-11-28 Guided Therapy Systems, L.L.C. System and method for fat and cellulite reduction
US9827449B2 (en) 2004-10-06 2017-11-28 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US9833639B2 (en) 2004-10-06 2017-12-05 Guided Therapy Systems, L.L.C. Energy based fat reduction
US9694212B2 (en) 2004-10-06 2017-07-04 Guided Therapy Systems, Llc Method and system for ultrasound treatment of skin
US8868958B2 (en) 2005-04-25 2014-10-21 Ardent Sound, Inc Method and system for enhancing computer peripheral safety
US9566454B2 (en) 2006-09-18 2017-02-14 Guided Therapy Systems, Llc Method and sysem for non-ablative acne treatment and prevention
JP2010527644A (en) * 2007-05-07 2010-08-19 ガイデッド セラピー システムズ, エル.エル.シー. Method and system for combining the acoustic energy using a coupler member, and collected at the focal
US9216276B2 (en) 2007-05-07 2015-12-22 Guided Therapy Systems, Llc Methods and systems for modulating medicants using acoustic energy
US9345910B2 (en) 2009-11-24 2016-05-24 Guided Therapy Systems Llc Methods and systems for generating thermal bubbles for improved ultrasound imaging and therapy
US9039617B2 (en) 2009-11-24 2015-05-26 Guided Therapy Systems, Llc Methods and systems for generating thermal bubbles for improved ultrasound imaging and therapy
US10183182B2 (en) 2010-08-02 2019-01-22 Guided Therapy Systems, Llc Methods and systems for treating plantar fascia
US9504446B2 (en) 2010-08-02 2016-11-29 Guided Therapy Systems, Llc Systems and methods for coupling an ultrasound source to tissue
US9149658B2 (en) 2010-08-02 2015-10-06 Guided Therapy Systems, Llc Systems and methods for ultrasound treatment
US8857438B2 (en) 2010-11-08 2014-10-14 Ulthera, Inc. Devices and methods for acoustic shielding
US9452302B2 (en) 2011-07-10 2016-09-27 Guided Therapy Systems, Llc Systems and methods for accelerating healing of implanted material and/or native tissue
US8858471B2 (en) 2011-07-10 2014-10-14 Guided Therapy Systems, Llc Methods and systems for ultrasound treatment
US9011337B2 (en) 2011-07-11 2015-04-21 Guided Therapy Systems, Llc Systems and methods for monitoring and controlling ultrasound power output and stability
US9263663B2 (en) 2012-04-13 2016-02-16 Ardent Sound, Inc. Method of making thick film transducer arrays
US9510802B2 (en) 2012-09-21 2016-12-06 Guided Therapy Systems, Llc Reflective ultrasound technology for dermatological treatments
US9802063B2 (en) 2012-09-21 2017-10-31 Guided Therapy Systems, Llc Reflective ultrasound technology for dermatological treatments

Similar Documents

Publication Publication Date Title
US4858613A (en) Localization and therapy system for treatment of spatially oriented focal disease
US9314650B2 (en) Method and apparatus for treatment of adipose tissue
US6217530B1 (en) Ultrasonic applicator for medical applications
US8690780B2 (en) Noninvasive tissue tightening for cosmetic effects
EP1498153B1 (en) Energy treatment apparatus
US7662098B2 (en) Ultrasonic probe and ultrasonic device
US7070565B2 (en) Solid hydrogel coupling for ultrasound imaging and therapy
US8690779B2 (en) Noninvasive aesthetic treatment for tightening tissue
RU2113171C1 (en) Device for carrying out ultrasonic therapeutic treatment
US6506171B1 (en) System and methods for controlling distribution of acoustic energy around a focal point using a focused ultrasound system
US7175599B2 (en) Shear mode diagnostic ultrasound
US4928672A (en) Shockwave source having a centrally disposed ultrasound locating system
US7520856B2 (en) Image guided high intensity focused ultrasound device for therapy in obstetrics and gynecology
ES2705758T3 (en) System for controlled heat treatment of human surface tissue
US5470350A (en) System for the treatment of pathological tissue having a catheter with a pressure sensor
US9261596B2 (en) Method for monitoring of medical treatment using pulse-echo ultrasound
CN1058905C (en) High-intensity focus supersonic tumour scanning therapy system
CN1294881C (en) Systems for reducing secondary hot spots in a phased array focused ultrasound system
US8133180B2 (en) Method and system for treating cellulite
JP4629034B2 (en) Ultrasonic shear mode treatment
EP0643982A1 (en) Ultrasound thermotherapy probe
JP2863506B2 (en) Transurethral formula Yuiase ultrasound therapy apparatus and method
CN100415318C (en) Systems for creating longer necrosed volumes using phased array focused ultrasound system
US20080177180A1 (en) Ultrasonic Image-Guided Tissue-Damaging Procedure
Child et al. Lung damage from exposure to pulsed ultrasound