JP2961903B2 - Ultrasonic three-dimensional imaging device - Google Patents
Ultrasonic three-dimensional imaging deviceInfo
- Publication number
- JP2961903B2 JP2961903B2 JP3016342A JP1634291A JP2961903B2 JP 2961903 B2 JP2961903 B2 JP 2961903B2 JP 3016342 A JP3016342 A JP 3016342A JP 1634291 A JP1634291 A JP 1634291A JP 2961903 B2 JP2961903 B2 JP 2961903B2
- Authority
- JP
- Japan
- Prior art keywords
- dimensional
- receiving
- ultrasonic
- output
- delay
- 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.)
- Expired - Fee Related
Links
Landscapes
- Closed-Circuit Television Systems (AREA)
- Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)
- Ultra Sonic Daignosis Equipment (AREA)
Description
【０００１】[0001]
【産業上の利用分野】本発明は、医用超音波診断装置や
非破壊検査装置等に用いられる超音波３次元撮像装置に
関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic three-dimensional imaging apparatus used for a medical ultrasonic diagnostic apparatus, a nondestructive inspection apparatus, and the like.
【０００２】[0002]
【従来の技術】従来技術は、特開昭62−12852 記載のよ
うに、１次元配列振動子を用いた２次元超音波像に対し
て、複数の受波ビームを形成する構成が提案されてい
る。２次元超音波像の場合、所望の分解能を得るのに必
要な１断層像内のビーム数は、１００〜２００本であ
る。例えば、撮像深度を１５cmとして、１本のビームを
送受信するのに必要な時間は０.２ｍsecである。従っ
て、送波ビーム１本に対し１〜２の受波ビームを同時形
成すれば、毎秒２５〜５０コマの撮像速度が得られ、動
きのある臓器に対してもリアルタイムで像が得られる。2. Description of the Related Art In the prior art, as described in Japanese Patent Application Laid-Open No. Sho 62-12852, there has been proposed a configuration in which a plurality of receiving beams are formed for a two-dimensional ultrasonic image using a one-dimensionally arranged transducer. I have. In the case of a two-dimensional ultrasonic image, the number of beams in one tomographic image required to obtain a desired resolution is 100 to 200. For example, assuming that the imaging depth is 15 cm, the time required for transmitting and receiving one beam is 0.2 msec. Therefore, if one or two receiving beams are simultaneously formed for one transmitting beam, an imaging speed of 25 to 50 frames per second can be obtained, and an image of a moving organ can be obtained in real time.
【０００３】[0003]
【発明が解決しようとする課題】３次元超音波像の場
合、所望の分解能を得るのに必要な１立体内のビーム数
は、２次元に対し１桁以上（例えば、１０倍）である。
従って、送波ビーム１本に対し１〜２本の受波ビームを
形成していたのでは、極端に撮像速度を低くするか、分
解能を劣化させて撮像速度を上げる必要があった。In the case of a three-dimensional ultrasonic image, the number of beams in one solid required to obtain a desired resolution is one digit or more (for example, 10 times) in two dimensions.
Therefore, if one or two reception beams are formed for one transmission beam, it is necessary to extremely lower the imaging speed or degrade the resolution to increase the imaging speed.
【０００４】[0004]
【課題を解決するための手段】上記問題点を解決する手
段として、１本の３次元送波方向に対し、等角度で複数
本（３本以上）の３次元受波ビームを同時形成する構成
とした。As a means for solving the above-mentioned problems, a configuration in which a plurality of (three or more) three-dimensional receiving beams are simultaneously formed at the same angle with respect to one three-dimensional transmitting direction. And
【０００５】[0005]
【作用】上記構成により、感度が均一な３次元受波ビー
ムが同時に多数形成できるので、高撮像速度で高分解能
な３次元超音波撮像が実現できる。According to the above configuration, since a large number of three-dimensional receiving beams having uniform sensitivity can be formed simultaneously, three-dimensional ultrasonic imaging with high imaging speed and high resolution can be realized.
【０００６】[0006]
【実施例】以下、図を用いて本発明の実施例を詳細に説
明する。DESCRIPTION OF THE PREFERRED EMBODIMENTS Embodiments of the present invention will be described below in detail with reference to the drawings.
【０００７】図１は、本発明による回路構成例を示す図
である。１は２次元配列振動子であり、３次元送波手段
２によって３次元送波ビームＴを形成する。１で受信さ
れた信号は、増幅手段３で増幅された後、３次元受波フ
ォーカス手段４により、例えば４方向の受波ビームＲ１
〜Ｒ４を同時形成する。４の出力は、検波、圧縮などの
信号処理手段５で信号処理され後、３次元メモリ手段６
に入力される。６の出力は、制御手段８の信号に従い、
表示手段７によって３次元表示、または任意断面表示さ
れる。送波ビーム方向Ｔ、及び受波ビーム方向Ｒ１〜Ｒ
４は制御手段８によって制御される。FIG. 1 is a diagram showing an example of a circuit configuration according to the present invention. Reference numeral 1 denotes a two-dimensional array transducer, which forms a three-dimensional transmission beam T by the three-dimensional transmission means 2. The signal received at 1 is amplified by the amplifying unit 3 and then received by the three-dimensional receiving focus unit 4, for example, a received beam R 1 in four directions.
To R4 are simultaneously formed. 4 is subjected to signal processing by signal processing means 5 for detection, compression, etc.
Is input to 6 outputs according to the signal of the control means 8
The display means 7 performs three-dimensional display or arbitrary cross-section display. Transmitting beam direction T and receiving beam directions R1 to R
4 is controlled by control means 8.
【０００８】図２は、２次元配列振動子１の素子分割例
を示す図である。（ａ）は矩形分割、（ｂ）は同心円と
放射線分割、（ｃ）は６角形分割の場合である。その他
の分割形状も考えられるが、どのような形状の２次元配
列素子分割においても、各素子の面積はほぼ等しくなる
ように分割した方が整相加算上良いことは明らかであ
る。また、送波ビームＴの指向性が、Ｔを中心軸とする
立体角円錐表面上でほぼ等しい感度となるように、図２
で示した２次元配列振動子の同心円内、または楕円面内
の素子を送受信駆動する。従って、ＴとＲ１〜Ｒ４の角
度をｒ１〜ｒ４として、ｒ１＝ｒ２＝ｒ３＝ｒ４となる
ように受波ビームを形成することにより、送受信感度が
均一なビームが同時に複数本形成できる。FIG. 2 is a diagram showing an example of element division of the two-dimensional array vibrator 1. (A) shows a case of rectangular division, (b) shows a case of concentric circle and radiation division, and (c) shows a case of hexagonal division. Although other divided shapes are conceivable, it is clear that in any shape of the two-dimensional array element division, it is better to divide the elements so that the area of each element is substantially equal in terms of phasing addition. 2 so that the directivity of the transmission beam T has substantially the same sensitivity on the surface of a solid angle cone with T as the central axis.
The elements in the concentric circles or the elliptical planes of the two-dimensional array vibrator shown in FIG. Therefore, by setting the angle between T and R1 to R4 as r1 to r4 and forming the receiving beam so that r1 = r2 = r3 = r4, a plurality of beams having uniform transmission / reception sensitivity can be formed simultaneously.
【０００９】図３は、本発明による受波整相回路４の回
路構成例を示すブロック図である。Ａ１〜Ａｎは図１の
増幅手段３の出力端子、ＭＰＸは選択手段である。ＭＰ
Ｘ出力は、可変口径、または可変フォーカスに従ってＡ
１〜Ａｎの隣接した任意の端子の組を選択し、第１の遅
延手段Ｐ１〜Ｐ４に入力される。Ｐ１〜Ｐ４では隣接端
子間（例えば、４端子）の位相合わせを行い、第２の遅
延手段Ｂ１〜Ｂ４に入力される。Ｂ１〜Ｂ４では各ブロ
ック間（例えば、４ブロック）の位相合わせを行い、そ
の各出力をａ，ｂ，ｃ，ｄとする。ａ，ｂ，ｃ，ｄを加
算することにより送波方向Ｔと同じ方向に受波ビームが
形成できる。そこで、ａ，ｂ，ｃ，ｄをバスラインＢＬ
を介して、第３の遅延手段Ｃ１〜Ｃ４にそれぞれ入力す
る。Ｃ１〜Ｃ４では送波方向Ｔに対して微小角ｒ１〜ｒ
４だけ受波ビームが偏向されるようにそれぞれ位相合わ
せを行い、加算手段Ｄ１〜Ｄ４によって加算される。Ｄ
１〜Ｄ４の出力が、送波方向Ｔに対して同時に形成され
る受波ビームＲ１〜Ｒ４となる。FIG. 3 is a block diagram showing an example of a circuit configuration of the wave receiving phasing circuit 4 according to the present invention. A1 to An are output terminals of the amplification means 3 in FIG. 1, and MPX is a selection means. MP
X output is A according to variable aperture or variable focus
An arbitrary set of adjacent terminals 1 to An is selected and input to the first delay means P1 to P4. In P1 to P4, the phases are adjusted between adjacent terminals (for example, four terminals) and input to the second delay means B1 to B4. In B1 to B4, the phases are adjusted between the blocks (for example, 4 blocks), and the respective outputs are a, b, c, and d. By adding a, b, c, and d, a receiving beam can be formed in the same direction as the transmitting direction T. Therefore, a, b, c, d are connected to the bus line BL.
, Are input to the third delay means C1 to C4, respectively. In C1 to C4, small angles r1 to r with respect to the transmission direction T
The phases are respectively adjusted so that the receiving beam is deflected by 4 and added by adding means D1 to D4. D
Outputs of 1 to D4 become reception beams R1 to R4 formed simultaneously in the transmission direction T.
【００１０】図４は、本発明による受波整相回路の別の
実施例を示す図である。Ａ１〜Ａｎ，ＭＰＸ，Ｐ１〜Ｐ
４は図３と同様のものである。ＡＤ１〜ＡＤ４はＡ／Ｄ
変換器、Ｍ１〜Ｍ４はメモリである。すなわち、Ｐ１〜
Ｐ４の出力は、ＡＤ１〜AD4によりＡ／Ｄ変換された
後、Ｍ１〜Ｍ４にそれぞれ記憶される。Ｍ１〜Ｍ４の出
力は、バスラインＢＬを介してデジタル遅延手段Ｅ１〜
Ｅ４に入力される。Ｅ１〜Ｅ４では、図３のＢ１〜Ｂ４
で行ったブロック間の位相合わせと、Ｃ１〜Ｃ４で行っ
た微小角ｒ１〜ｒ４の位相合わせを同時に行う。Ｅ１〜
Ｅ４の各出力は、デジタル加算手段Ｆ１〜Ｆ４によりそ
れぞれ加算され、受波ビームＲ１〜Ｒ４を形成する。FIG. 4 is a diagram showing another embodiment of the wave receiving and phasing circuit according to the present invention. A1-An, MPX, P1-P
4 is the same as FIG. AD1 to AD4 are A / D
The converters, M1 to M4, are memories. That is, P1
The output of P4 is stored in M1 to M4 after A / D conversion by AD1 to AD4. The outputs of M1 to M4 are connected to digital delay means E1 to E1 via bus line BL.
Input to E4. In E1 to E4, B1 to B4 in FIG.
And the phase adjustment of the small angles r1 to r4 performed at C1 to C4 are performed simultaneously. E1
The outputs of E4 are added by digital adding means F1 to F4, respectively, to form received beams R1 to R4.
【００１１】上記実施例では、４ブロックの第２遅延手
段から４本の受波ビームを同時形成する場合について説
明したが、任意数ブロックの第２遅延手段から４本以上
の受波ビームを同時形成する場合にも適応可能なことは
明らかである。また、第１遅延手段によりブロック分割
することなしに、各素子Ａ１〜Ａｎの受波信号から第
２、及び第３遅延手段により直接複数の受波ビームを形
成することも可能である。In the above embodiment, a case has been described in which four received beams are simultaneously formed from four blocks of second delay means. However, four or more received beams are simultaneously formed from any number of blocks of second delay means. Obviously, it can be applied to the case of forming. Further, it is also possible to directly form a plurality of received beams by the second and third delay units from the received signals of the elements A1 to An without dividing the block by the first delay unit.
【００１２】[0012]
【発明の効果】感度が均一な３次元受波ビームが同時に
多数形成できるので、高撮像速度で高分解能な３次元超
音波撮像が実現できる。Since a large number of three-dimensional receiving beams having uniform sensitivity can be formed at the same time, high-resolution three-dimensional ultrasonic imaging at a high imaging speed can be realized.
【図１】本発明の実施例による回路構成例を示す図。FIG. 1 is a diagram showing an example of a circuit configuration according to an embodiment of the present invention.
【図２】２次元配列振動子の素子分割例を示す図。FIG. 2 is a diagram showing an example of element division of a two-dimensional array transducer.
【図３】本発明の実施例による受波整相回路の回路構成
例を示すブロック図。FIG. 3 is a block diagram showing a circuit configuration example of a wave receiving phasing circuit according to an embodiment of the present invention.
【図４】本発明による受波整相回路の別の実施例を示す
図。FIG. 4 is a diagram showing another embodiment of the wave receiving phasing circuit according to the present invention.
１…２次元配列振動子、２…３次元送波フォーカス手
段、３…増幅手段、４…３次元受波フォーカス手段、５
…信号処理手段、６…３次元メモリ、７…表示手段、８
…制御手段、ＭＰＸ…選択手段、Ｐ１〜Ｐ４…第１遅延
手段、Ｂ１〜Ｂ４…第２遅延手段、Ｃ１〜Ｃ４…第３遅
延手段，Ｄ１〜Ｄ４…加算手段、ＡＤ１〜ＡＤ４…Ａ／
Ｄ変換器、Ｍ１〜Ｍ４…メモリ、Ｅ１〜Ｅ４…デジタル
遅延手段、Ｆ１〜Ｆ４…デジタル加算手段。DESCRIPTION OF SYMBOLS 1 ... Two-dimensional array oscillator, 2 ... Three-dimensional transmission focus means, 3 ... amplification means, 4 ... Three-dimensional reception focus means, 5
... Signal processing means, 6 ... 3-dimensional memory, 7 ... Display means, 8
... Control means, MPX ... Selection means, P1-P4 ... First delay means, B1-B4 ... Second delay means, C1-C4 ... Third delay means, D1-D4 ... Addition means, AD1-AD4 ... A /
D converters, M1 to M4 ... memories, E1 to E4 ... digital delay means, F1 to F4 ... digital addition means.
───────────────────────────────────────────────────── フロントページの続き (72)発明者 鱒澤 裕 東京都国分寺市東恋ケ窪１丁目280番地 株式会社 日立製作所 中央研究所内 (72)発明者 菊池 隆文 東京都国分寺市東恋ケ窪１丁目280番地 株式会社 日立製作所 中央研究所内 (56)参考文献 特開 平２−203848（ＪＰ，Ａ) 特開 昭63−99846（ＪＰ，Ａ) (58)調査した分野(Int.Cl.6，ＤＢ名) G01N 29/00 - 29/28 A61B 8/14 ──────────────────────────────────────────────────続 き Continuing on the front page (72) Inventor Hiroshi Masuzawa 1-280 Higashi Koikekubo, Kokubunji-shi, Tokyo Inside the Central Research Laboratory, Hitachi, Ltd. (56) References JP-A-2-203848 (JP, A) JP-A-63-99846 (JP, A) (58) Fields investigated (Int. Cl. 6 , DB name) G01N 29 / 00-29/28 A61B 8/14
Claims (2)
超音波ビームを３次元的に収束して送波する３次元送波
フォーカス手段と、前記２次元配列振動子の受波信号群
に遅延分布を与えて加算することにより超音波受波ビー
ムを形成する３次元受波フォーカス手段と、該３次元受
波フォーカス手段の出力を信号処理する信号処理手段
と、該信号処理手段の出力を記憶するメモリ手段と、該
メモリ手段の出力を表示する表示手段と、前記各手段を
制御する制御手段とを有し、上記３次元受波フォーカス
手段は、送波された超音波ビームの中心軸から周辺にそ
れぞれ微小角だけずれた複数の方向にそれぞれ収束する
複数の受波ビームを同時に形成することを特徴とする超
音波３次元撮像装置。1. A two-dimensional array transducer for transmitting and receiving ultrasonic waves,
Three-dimensional transmission focusing means for three-dimensionally converging and transmitting an ultrasonic beam, and a reception signal group of the two-dimensional array transducer
Receiving means for forming an ultrasonic receiving beam by giving a delay distribution to the signals and adding them, a signal processing means for performing signal processing on an output of the three-dimensional receiving focusing means, and an output of the signal processing means a memory means for storing and display means for displaying the output of said memory means, and control means for controlling said each means, the three-dimensional reception focus
The means extends from the central axis of the transmitted ultrasonic beam to the periphery.
Converge in multiple directions, each shifted by a small angle
An ultrasonic three-dimensional imaging apparatus, wherein a plurality of receiving beams are simultaneously formed .
元配列振動子の受波信号に対し、送波された超音波ビー
ムの中心軸からの反射波に位相合わせする遅延分布を与
える第１の遅前手段と、該第１の遅延手段の出力群をそ
れぞれが入力し、それぞれが前記出力群に対し受波ビー
ムの方向をそれぞれ微小角だけ偏向させる遅延分布を与
える複数の第２の遅延手段を含むことを特徴とする請求
項１記載の超音波３次元撮像装置。2. The three-dimensional wave receiving focus means for giving a delay distribution for adjusting a phase of a received signal of each two-dimensionally arranged transducer to a reflected wave from a central axis of a transmitted ultrasonic beam. A plurality of second delay units, each of which receives the output group of the first delay unit and the output group of the first delay unit, and provides the output group with a delay distribution for deflecting the direction of the received beam by a small angle. The ultrasonic three-dimensional imaging apparatus according to claim 1, further comprising a delay unit.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3016342A JP2961903B2 (en) | 1991-02-07 | 1991-02-07 | Ultrasonic three-dimensional imaging device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3016342A JP2961903B2 (en) | 1991-02-07 | 1991-02-07 | Ultrasonic three-dimensional imaging device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH04254754A JPH04254754A (en) | 1992-09-10 |
| JP2961903B2 true JP2961903B2 (en) | 1999-10-12 |
Family
ID=11913723
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP3016342A Expired - Fee Related JP2961903B2 (en) | 1991-02-07 | 1991-02-07 | Ultrasonic three-dimensional imaging device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2961903B2 (en) |
Families Citing this family (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6866634B2 (en) * | 2000-05-09 | 2005-03-15 | Hitachi Medical Corporation | Ultrasonic diagnostic apparatus |
| ATE356403T1 (en) * | 2000-08-24 | 2007-03-15 | Koninkl Philips Electronics Nv | DYNAMIC MICRO-BEAM FORMING ULTRASONIC DIAGNOSTIC IMAGING SYSTEM |
| JP4522687B2 (en) * | 2002-11-13 | 2010-08-11 | 富士フイルム株式会社 | Ultrasonic imaging method and ultrasonic imaging apparatus |
| CN100435740C (en) * | 2003-08-14 | 2008-11-26 | 松下电器产业株式会社 | Ultrasonographic device |
| JP4593260B2 (en) * | 2004-12-16 | 2010-12-08 | パナソニック株式会社 | Ultrasonic diagnostic equipment |
| WO2008126015A1 (en) * | 2007-04-13 | 2008-10-23 | Koninklijke Philips Electronics, N.V. | High speed ultrasonic thick slice imaging |
| JP5627171B2 (en) * | 2008-06-26 | 2014-11-19 | 株式会社東芝 | Ultrasonic diagnostic equipment |
| JP5649576B2 (en) * | 2008-09-15 | 2015-01-07 | テラテク・コーポレーシヨン | 3D ultrasonic imaging system |
| US20100081936A1 (en) * | 2008-09-29 | 2010-04-01 | Kazuhito Nakata | Ultrasonic diagnosis apparatus and ultrasonic transmission/reception method |
| JP5315153B2 (en) * | 2009-07-21 | 2013-10-16 | 日立アロカメディカル株式会社 | Ultrasonic diagnostic equipment |
| JP5436965B2 (en) | 2009-07-28 | 2014-03-05 | 日立アロカメディカル株式会社 | Ultrasonic diagnostic equipment |
-
1991
- 1991-02-07 JP JP3016342A patent/JP2961903B2/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| JPH04254754A (en) | 1992-09-10 |
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| Date | Code | Title | Description |
|---|---|---|---|
| LAPS | Cancellation because of no payment of annual fees |