JP2008307087A - Ultrasonogaph - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To improve local sensitivity degradation on image data which are caused by ultrasonic absorption in transmitting ultrasound in tissues of a subject and an obstruction preventing the transmission. <P>SOLUTION: An ultrasonograph 100 is equipped with two ultrasonic probes 4a, 4b disposed in different positions of the subject. First, first three-dimensional ultrasound data are generated by using the ultrasonic probe 4a selected by a probe selection part 3, and second three-dimensional ultrasonic data are generated by using the ultrasonic probe 4b selected in the same way. Then, third volume data are generated by combining a first volume data based on the first three-dimensional ultrasonic data and a second volume data based on the second three-dimensional ultrasonic data, and three-dimensional image data acquired by performing rendering processing on the third volume data are displayed on a display part 9. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and in particular, it is possible to generate high-quality image data by synthesizing ultrasonic information collected by each of a plurality of ultrasonic probes arranged on the same subject. The present invention relates to an ultrasonic diagnostic apparatus.

  The ultrasonic diagnostic apparatus performs ultrasonic transmission / reception in a plurality of directions in a subject using an ultrasonic probe in which a plurality of vibration elements are arranged, and monitors image data generated based on the reflected wave obtained at this time It is displayed on the top and is widely used for morphological diagnosis and functional diagnosis of various organs because it can observe a two-dimensional image in the body in real time with a simple operation by simply bringing an ultrasonic probe into contact with the body surface. Yes.

  In recent years, a method of collecting three-dimensional data (volume data) by further mechanically moving an ultrasonic probe in which a plurality of vibration elements are arranged one-dimensionally, or a plurality of ultrasonic transducers are arranged two-dimensionally A method for collecting volume data using a so-called two-dimensional array ultrasonic probe has been developed, and attempts have been made to display three-dimensional image data such as volume rendering image data generated based on the volume data in real time. .

By observing the three-dimensional image data obtained in this way, it becomes easy to grasp the positional relationship between blood vessels and organs, and therefore, application to invasive examinations and treatments has been studied. By performing puncture for the purpose of drug administration and cell / tissue extraction under observation of three-dimensional image data, safety in examination and treatment can be dramatically improved (see, for example, Patent Document 1) .).
JP 2006-346176 A

  However, when collecting three-dimensional image data using one ultrasonic probe, when sufficient S / N cannot be obtained due to ultrasonic absorption generated when ultrasonic waves propagate through the subject tissue, There has been a limit to gain correction of received signals by the TGC (Time Gain Control) method that has been performed conventionally. In addition, when there are lungs, bones, etc. that prevent the propagation of ultrasonic waves in the ultrasonic wave transmission / reception direction, the diagnostic ability of the ultrasonic diagnostic apparatus is significantly reduced because the biological tissue information behind them cannot be captured. Had problems.

  The present invention has been made in view of the above-described problems, and an object of the present invention is to absorb the ultrasonic waves when the ultrasonic waves propagate through the tissue of the subject and images due to the above-described obstacles that prevent the propagation. An object of the present invention is to provide an ultrasonic diagnostic apparatus that can improve local sensitivity deterioration on data.

  In order to solve the above problems, an ultrasonic diagnostic apparatus according to the present invention according to claim 1 is an ultrasonic diagnostic apparatus that generates image data based on volume data obtained by three-dimensional scanning of ultrasonic waves on a subject. A plurality of ultrasonic probes that perform the three-dimensional scanning from a plurality of different directions of the subject, position detection means that detects position information of the ultrasonic probes, and each of the plurality of ultrasonic probes. Volume data generating means for generating a plurality of volume data based on reception signals collected by three-dimensional scanning of the subject, and volume data combining means for combining the plurality of volume data based on position information of the ultrasonic probe; Image data generating means for processing the synthesized volume data to generate image data; and the image data Is characterized by comprising display means for displaying the data.

  According to a third aspect of the present invention, there is provided an ultrasonic diagnostic apparatus for generating image data based on volume data obtained by three-dimensional scanning of ultrasonic waves on a subject. A plurality of ultrasonic probes that perform the three-dimensional scanning from a plurality of directions, a position detection unit that detects position information of the ultrasonic probes, and a three-dimensional scanning of the subject using each of the plurality of ultrasonic probes Volume data generating means for generating a plurality of volume data based on the received signal collected by the image processing apparatus; image data generating means for processing each of the plurality of volume data to generate a plurality of image data; and the plurality of image data Is synthesized based on the position information of the ultrasonic probe, and a display for displaying the synthesized image data It is characterized in that a stage.

  According to the present invention, it is possible to reduce the local sensitivity deterioration on the image data caused by the absorption of the ultrasonic wave when the ultrasonic wave propagates through the tissue of the subject and the obstacle that prevents the propagation. Three-dimensional image data can be collected.

  Embodiments of the present invention will be described below with reference to the drawings.

  The ultrasonic diagnostic apparatus according to the first embodiment of the present invention described below includes two ultrasonic probes arranged at different positions of the subject. First, first three-dimensional ultrasonic data is generated using a first ultrasonic probe, and then second three-dimensional ultrasonic data is generated using a second ultrasonic probe. Next, the first volume data based on the first three-dimensional ultrasonic data and the second volume data based on the second three-dimensional ultrasonic data are synthesized to generate third volume data. The third volume data is rendered to generate 3D image data.

  In the first embodiment described below, a case will be described in which a three-dimensional scan is performed on a region to be diagnosed of the subject using an ultrasonic probe having a plurality of vibration elements arranged two-dimensionally. However, the present invention is not limited to this. For example, the diagnosis target region may be scanned three-dimensionally by swinging or moving a plurality of one-dimensionally arranged vibration elements in a direction orthogonal to the arrangement direction.

  In this embodiment, the case where three-dimensional image data is generated based on B-mode data will be described. However, three-dimensional image data based on other ultrasonic data such as color Doppler data, or B-mode data and color Doppler data. It may be 3D image data based on it.

(Device configuration)
The configuration of the ultrasonic diagnostic apparatus according to this embodiment will be described with reference to FIGS. FIG. 1 is a block diagram showing an overall configuration of the ultrasonic diagnostic apparatus, and FIG. 3 is a block diagram showing a specific configuration of a transmission / reception unit and an ultrasonic data generation unit provided in the ultrasonic diagnostic apparatus. is there. FIG. 6 is a block diagram showing a specific configuration of an image data generation unit provided in the ultrasonic diagnostic apparatus.

  The ultrasonic diagnostic apparatus 100 of the present embodiment shown in FIG. 1 transmits an ultrasonic pulse (transmitted ultrasonic wave) to a diagnosis target part of a subject, and an ultrasonic reflected wave (received ultrasonic wave) obtained by this transmission. ) Two ultrasonic probes 4a (first ultrasonic probe) and ultrasonic probe 4b (second ultrasonic probe) having a plurality of vibration elements that convert electrical signals (reception signals) into ultrasonic signals, and ultrasonic waves The probe selection unit 3 that selects the probe 4a or the ultrasonic probe 4b, and the ultrasonic probe 4a or the ultrasonic signal that is selected by the probe selection unit 3 as a drive signal for transmitting an ultrasonic pulse in a predetermined direction of the subject. A transmission / reception unit 2 that supplies the oscillating element of the sonic probe 4b and phasing and adding the reception signals of a plurality of channels obtained from these oscillating elements via the probe selection unit 3; 3 obtained by three-dimensional scanning with respect to the subject using the ultrasonic data generation unit 5 that generates ultrasonic data (B-mode data) by performing signal processing on the signal, and the ultrasonic probe 4a and the ultrasonic probe 4b. A volume data generation unit 6 that generates volume data using dimensional ultrasonic data (hereinafter referred to as three-dimensional ultrasonic data) is provided.

  Furthermore, the ultrasonic diagnostic apparatus 100 uses the volume data (first volume data) generated using the ultrasonic probe 4a and the volume data (second volume data) generated using the ultrasonic probe 4b. A volume data synthesizing unit 7 for synthesizing based on the positional information of the acoustic probes 4a and 4b and generating third volume data; and an image data generating unit 8 for generating three-dimensional image data using the third volume data; A display unit 9 for displaying the generated three-dimensional image data, an input unit 10 for inputting subject information, setting image data collection conditions and image data display conditions, and inputting various command signals, and an ultrasonic probe. Position detection unit 11a (first position detection unit) that detects position information of 4a and position detection that detects position information of the ultrasonic probe 4b 11b (second position detector), and a system control unit 12 which collectively controls the respective units described above.

  Each of the ultrasonic probes 4a and 4b slidably or swingably attached to a support (not shown) arranged around the subject has N vibration elements (not shown) arranged two-dimensionally at its tip. The tip is brought into contact with the patient's body surface to transmit and receive ultrasonic waves. These N vibrating elements are connected to the input / output terminals of the transmission / reception unit 2 via an N-channel multi-core cable and the probe selection unit 3.

  The vibration element is an electroacoustic transducer, which converts an electric pulse (drive signal) into an ultrasonic pulse (transmitted ultrasonic wave) at the time of transmission, and converts an ultrasonic reflected wave (received ultrasonic wave) into an electric reception signal at the time of reception. It has the function to convert to. The ultrasonic probes 4a and 4b include sector scanning, linear scanning, convex scanning, and the like, and the operator can arbitrarily select them according to the diagnostic site. A case will be described in which sector scanning ultrasonic probes 4a and 4b in which N vibrating elements are two-dimensionally arranged are used.

  Next, the function of the probe selection unit 3 will be described with reference to FIG. However, here, in order to simplify the description, a case will be described in which the number of vibration elements for transmission (Nt) and the number of vibration elements for reception (Nr) are equal to the number N of vibration elements included in the ultrasonic probe 4a or the ultrasonic probe 4b. However, the present invention is not limited to this.

  That is, as shown in FIG. 2, the probe selection unit 3 has N-channel change-over switches SW-1 to SW-N, and each of these change-over switches SW-1 to SW-N is supplied from the system control unit 12. One of the vibration elements 41a-1 to 41a-N built in the ultrasonic probe 4a or the vibration elements 41b-1 to 41b-N built in the ultrasonic probe 4b according to the selected control signal is transmitted to the transmission unit 2 21-1 to 21-N and receiving units 22-1 to 22-N are connected.

  Next, the transmission / reception unit 2 illustrated in FIG. 3 transmits a drive signal to Nt transmission vibration elements selected from the N vibration elements in the ultrasonic probe 4a or the ultrasonic probe 4b. 21 and a receiving unit 22 that performs phasing addition on the received signal of the Nr channel obtained by Nr receiving vibrating elements selected from the N vibrating elements.

  The transmission unit 21 includes a rate pulse generator 211, a transmission delay circuit 212, and a drive circuit 213. The rate pulse generator 211 generates a rate pulse that determines the repetition period of the transmission ultrasonic wave and supplies the generated rate pulse to the transmission delay circuit 212. To do. The transmission delay circuit 212 is composed of the same number of independent delay circuits as the Nt number of vibration elements used for transmission, and includes a focusing delay time for focusing the transmission ultrasonic wave to a predetermined depth and a predetermined direction (θp, A deflection delay time for transmission to φq) is given to the rate pulse and supplied to the drive circuit 213. The drive circuit 213 includes the same number of independent drive circuits as the transmission delay circuit 212, and Nt (Nt ≦ Nt ≦ N) selected for transmission from among the N vibration elements arranged two-dimensionally by the ultrasonic probe 3 N) Driving the number of vibration elements to radiate transmission ultrasonic waves into the body of the subject.

  On the other hand, the receiving unit 22 has Nr channels corresponding to Nr (Nr ≦ N) vibration elements selected for reception from among the N vibration elements built in the ultrasonic probe 4a or the ultrasonic probe 4b. The preamplifier 220, the A / D converter 221, the reception delay circuit 222, and the adder 223 are provided. Each of the Nr channel received signals supplied from the receiving vibration element is corrected for attenuation depending on the propagation distance of the living tissue in the preamplifier 220, and further converted into a digital signal by the A / D converter 221. And sent to the reception delay circuit 222.

  The reception delay circuit 222 sets a focusing delay time for focusing the received ultrasonic wave from a predetermined depth and a deflection delay time for setting a strong reception directivity for a predetermined direction (θp, φq). An Nr channel reception signal output from the / D converter 221 is applied to each of the reception signals, and an adder 223 adds and combines the reception signals from the reception delay circuit 222. That is, the reception delay circuit 222 and the adder 223 perform phasing addition on the reception signal obtained from a predetermined direction.

  FIG. 4 shows the ultrasonic transmission / reception direction (θp, φq) in orthogonal coordinates (xo-yo-zo) set with the central axis of the ultrasonic probe 4a as the z-axis. In this case, the vibration element Are two-dimensionally arranged along the xo-axis direction and the yo-axis direction, and θp and φq indicate angles with respect to the zo-axis in the transmission / reception direction projected on the xo-zo plane and the yo-zo plane.

  Note that the reception delay circuit 222 and the adder 223 can perform so-called parallel simultaneous reception in which a reception ultrasonic beam in a plurality of directions is simultaneously formed by delay time control of the system control unit 12. By applying this parallel simultaneous reception method, the time required for three-dimensional scanning is greatly reduced.

  Returning to FIG. 3, the ultrasonic data generation unit 5 includes an envelope detector 51 and a logarithmic converter 52, and the received signal after phasing addition supplied from the adder 223 of the reception unit 22 is envelope detection. After the envelope is detected by the device 51, the logarithmic converter 52 logarithmically converts the amplitude thereof to generate B-mode data as ultrasonic data. Note that the envelope detector 51 and the logarithmic converter 52 may be configured by changing the order. The ultrasonic data generated by the ultrasonic data generation unit 5 is stored in a data storage circuit (not shown) of the volume data generation unit 6.

  Next, the volume data generation unit 6 shown in FIG. 1 performs three-dimensional ultrasound data (first three-dimensional ultrasound data) and ultrasound collected by three-dimensional scanning on the subject using the ultrasound probe 4a. The above-described data storage circuit for storing three-dimensional ultrasonic data (second three-dimensional ultrasonic data) collected by three-dimensional scanning on the subject using the probe 4b and interpolation processing of these three-dimensional ultrasonic data And an arithmetic circuit for generating the first volume data and the second volume data.

  That is, the ultrasonic data collected by the three-dimensional scanning of the subject using the ultrasonic probes 4a and 4b corresponds to the data in the transmission / reception direction (θp, φq) supplied from the system control unit 12. The first three-dimensional ultrasonic data and the second three-dimensional ultrasonic data are generated in the storage circuit.

  On the other hand, the arithmetic circuit reads out the first three-dimensional ultrasonic data and the second three-dimensional ultrasonic data generated by the data storage circuit, and sets the three-dimensional ultrasonic data at unequal intervals. Volume data having isotropic voxels is generated by interpolating the voxels.

  Next, the volume data synthesizing unit 7 has an arithmetic circuit (not shown), and the position information of the ultrasonic probes 4a and 4b detected by the position detecting units 11a and 11b and supplied via the main control unit 122 of the system control unit 12 is provided. Based on (for example, the position coordinates and inclination angles of the ultrasonic probes 4a and 4b), the first volume data supplied from the volume data generation unit 6 and the second volume data are combined to generate the third volume data. .

  FIG. 5 is a diagram for explaining a method of synthesizing the first volume data and the second volume data by the volume data synthesizing unit 7. In this figure, the position information supplied from the position detecting units 11a and 11b is shown. The first volume data Va and the second volume data Vb synthesized based on the above are shown. In this case, the voxel value Px (Lax, Lbx) of the voxel Bx in the third volume data separated from the ultrasonic probe 4a by the distance Lax and separated from the ultrasonic probe 4b by the distance Lbx (Lbx> Lax) is the first volume data. The voxel value of the voxel Bx in Va and the voxel value of the voxel Bx in the second volume data Vb are calculated by weighted addition based on the distances Lax and Lbx.

For example, when the voxel value of the voxel Bx in the first volume data Va is Pa and the voxel value of the voxel Bx in the second volume data Vb is Pb, the voxel value Px (Lax, Lbx) is calculated by, for example, the following formula (1) or (2), and the voxel value Pa of the first volume data Va collected by the ultrasonic probe 4a close to the voxel Bx is dominant. A weighting process is performed.

  Next, a method for generating three-dimensional image data by the image data generation unit 8 will be described with reference to FIG. FIG. 6 is a block diagram illustrating a specific configuration of the image data generation unit 8 that enables generation of three-dimensional image data. The image data generation unit 8 includes a volume data storage unit 81, an opacity / tone setting, and the like. A unit 82, a rendering processing unit 83, and a three-dimensional image data storage unit 84. Then, the third volume data generated by combining the first volume data and the second volume data in the volume data combining unit 7 is temporarily stored in the volume data storage unit 81.

  On the other hand, the opacity / color tone setting unit 82 sets the transparency and the color tone in units of voxels based on the voxel value of the third volume data, and the rendering processing unit 83 sets the non-transparency set by the opacity / color tone setting unit 82. Based on the transparency and color tone information, the third volume data supplied from the volume data storage unit 81 is rendered to generate three-dimensional image data. The obtained three-dimensional image data is stored in the three-dimensional image data storage unit 84.

  Returning to FIG. 1 again, the display unit 9 includes a display data generation unit, a data conversion unit, and a monitor (not shown). The display data generation unit adds display information such as subject information supplied from the input unit 10 via the system control unit 12 to the three-dimensional image data generated by the image data generation unit 8 to display the display data. Generate. The data conversion unit performs D / A conversion and display format conversion on the display data and displays the display data on the monitor.

  Next, the input unit 10 is an interactive interface including input devices such as a display panel, a keyboard, various switches, a selection button, a mouse, and a trackball. The input unit 10 inputs subject information, sets image data collection conditions, and images. Setting of data display conditions, selection of ultrasonic data acquisition mode (B mode data acquisition mode, color Doppler data acquisition mode, etc.), and input of various command signals, etc. are performed using the above-described display panel and input device. .

  On the other hand, each of the position detector 11a attached to the ultrasonic probe 4a and the position detector 11b attached to the ultrasonic probe 4b has a function of detecting the position coordinates, the inclination angle, etc. of the ultrasonic probes 4a and 4b. is doing. Various methods have been proposed as a method for detecting the position of an ultrasonic probe. However, in consideration of detection accuracy, cost, size, and the like, a method using an ultrasonic sensor or a magnetic sensor is preferable. For example, the position detectors 11a and 11b having magnetic sensors include a transmitter (magnet generator) that generates magnetism and a plurality of magnets that detect the magnetism as described in Japanese Patent Application Laid-Open No. 2000-5168. A receiver having a sensor, and a position information calculation unit that processes an electrical signal (detection signal) based on the detected magnetism and calculates information (position information) on the positions and inclinations of the ultrasonic probes 4a and 4b (both are both) (Not shown). The receiver having a magnetic sensor is usually mounted on the surface of the ultrasonic probes 4a and 4b, and the transmitter is installed in the vicinity of the ultrasonic probes 4a and 4b. Then, the position information calculation unit calculates the position information of the ultrasonic probes 4a and 4b based on the distance between each of the plurality of magnetic sensors measured by magnetism and the transmitter (that is, the position coordinates of the ultrasonic probes 4a and 4b, (Tilt angle) is calculated.

  The system control unit 12 includes a scanning control unit 121 and a main control unit 122. The scanning control unit 121 controls delay times in the transmission delay circuit 212 of the transmission unit 21 and the reception delay circuit 222 of the reception unit 22 based on the collection conditions of image data supplied from the input unit 10 via the main control unit 122. To do.

  On the other hand, the main control unit 122 includes a CPU and a storage circuit (not shown), and the storage circuit stores the above-described subject information input / set / selected by the input unit 10 and image data collection conditions. Then, the CPU comprehensively controls each unit of the ultrasonic diagnostic apparatus 100 based on the above-mentioned input information / setting information / selection information and pre-stored setting information / selection information to generate three-dimensional image data. Display.

  FIG. 7 is a diagram for explaining the selection control of the ultrasound probes 4a and 4b and the transmission / reception direction switching control for these ultrasound probes 4a and 4b. For simplicity of explanation, the ultrasound probes 4a and 4b are illustrated. 1 shows a case where two-dimensional ultrasonic data is collected by performing ultrasonic transmission / reception in the transmission / reception directions θ1 to θP, but actually, the transmission / reception direction (θp, φq) (θp = θ1 + (p−1) ) The above-mentioned three-dimensional ultrasonic data is collected by ultrasonic transmission / reception for Δθ (p = 1 to P), φq = φ1 + (q−1) Δφ (q = 1 to Q)).

  That is, as shown in FIG. 7, in the present embodiment, the superposition with respect to the transmission / reception directions θ1 to θP ((θp, φq) p = 1 to P, q = 1 to Q) with respect to the central axis Axa of the ultrasonic probe 4a. Transmission / reception of sound waves and transmission / reception of ultrasonic waves in the transmission / reception directions θ1 to θP ((θp, φq) p = 1 to P, q = 1 to Q) with reference to the central axis Axb of the ultrasonic probe 4b are alternately repeated. Done.

(3D image data collection procedure)
Next, the procedure for collecting the three-dimensional image data in this embodiment will be described with reference to the flowchart of FIG. Prior to the ultrasound three-dimensional scanning of the subject, the operator of the ultrasound diagnostic apparatus 100 inputs subject information at the input unit 10 and then sets image data collection conditions and image data display conditions. (Step S1 in FIG. 8).

  Next, the operator places the distal end portions of the ultrasonic probes 4a and 4b on the body surface of the subject, and inputs a 3D image data collection start command at the input unit 10 (step S2 in FIG. 8). Then, when this command signal is supplied to the main control unit 122 of the system control unit 12, the collection of the three-dimensional image data is started.

  When collecting the three-dimensional image data, the main control unit 122 of the system control unit 12 supplies a selection control signal to the probe selection unit 3, and the vibration elements 41 a-1 to 41 a -N of the ultrasonic probe 4 a and the transmission / reception unit 2. The rate pulse generator 211 of the transmission unit 21 generates a rate pulse according to the control signal supplied from the main control unit 122 of the system control unit 12 and transmits the transmission delay. Supply to circuit 212.

  The transmission delay circuit 212 is a transmission / reception direction (θ1,...) Based on the delay time for focusing the transmission ultrasonic wave based on the control signal supplied from the scanning control unit 121 of the system control unit 12 and the central axis of the ultrasonic probe 4a. A delay time for transmitting the transmission ultrasonic wave is given to the rate pulse to φ1), and this rate pulse is supplied to the drive circuit 213 of the Nt channel. Next, the drive circuit 213 generates a drive signal based on the rate pulse supplied from the transmission delay circuit 212, and supplies this drive signal to the Nt number of vibration elements 41a in the ultrasonic probe 4a via the probe selection unit 3. Transmitting ultrasonic waves into the body of the subject.

  A part of the radiated transmission ultrasonic wave is reflected at a boundary between tissues having different acoustic impedances and converted into a reception signal by the vibration element 41a. Next, the reception signal supplied to the reception unit 22 via the probe selection unit 3 is converted into a digital signal by the A / D converter 221 of the reception unit 22, and then the Nr channel reception delay circuit 222 has a predetermined depth. A focusing delay time for focusing the received ultrasonic wave and a deflection delay time for setting a strong reception directivity with respect to the receiving ultrasonic wave from the transmission / reception direction (θ1, φ1) are given. Phased and added at.

  The ultrasonic data generation unit 5 to which the reception signal after the phasing addition is supplied performs envelope detection and logarithmic conversion on the reception signal to generate ultrasonic data (B mode data), and volume data. The data is stored in the data storage circuit of the generation unit 6.

  When the generation and storage of the ultrasound data for the transmission / reception direction (θ1, φ1) is completed, the scanning control unit 121 of the system control unit 12 performs the transmission delay circuit 212 of the transmission unit 21 and the reception delay circuit 222 of the reception unit 22. The transmission / reception direction of ultrasonic waves is sequentially updated by Δθ in the θ direction and Δφ in the φ direction by controlling the delay time (θp, φq) (θp = θ1 + (p−1) Δθ (p = 2 to P), φq. = Φ1 + (q−1) Δφ (q = 2 to Q)), ultrasonic transmission / reception is performed in the same procedure as in the transmission / reception direction (θ1, φ1) to perform three-dimensional scanning on the subject. The ultrasonic data obtained in each transmission / reception direction is sequentially stored in the data storage circuit of the volume data generation unit 6 to generate three-dimensional ultrasonic data (first three-dimensional ultrasonic data) (FIG. 8 step S4).

  When the collection of the first three-dimensional ultrasonic data by the ultrasonic probe 4a is completed, the main control unit 122 of the system control unit 12 supplies the selection control signal to the probe selection unit 3 again to supply the ultrasonic probe 4b. Are connected to the input / output terminals of the transmission / reception unit 2 (step S5 in FIG. 8), the scanning control unit 121 of the system control unit 12 includes the transmission delay circuit 212 of the transmission unit 21 and Transmission / reception direction (θp, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P) with reference to the central axis of the ultrasonic probe 4b by controlling the delay time in the reception delay circuit 222 of the reception unit 22 , Φq = φ1 + (q−1) Δφ (q = 1 to Q)), three-dimensional scanning is performed on the subject by transmitting and receiving ultrasonic waves in the same procedure as in the case of the ultrasonic probe 4a. The ultrasonic data obtained in each transmission / reception direction is sequentially stored in the data storage circuit of the volume data generation unit 6 to generate three-dimensional ultrasonic data (second three-dimensional ultrasonic data) (see FIG. 8 step S6).

  When the collection of the first three-dimensional ultrasonic data by the ultrasonic probe 4a and the second three-dimensional ultrasonic data by the ultrasonic probe 4b is completed, the arithmetic circuit of the volume data generation unit 6 is the own data storage circuit. The first three-dimensional ultrasound data and the second three-dimensional ultrasound data generated in step 1 are read out, and the voxels constituting these three-dimensional ultrasound data are interpolated to form isotropic voxels. First volume data and second volume data are generated (step S7 in FIG. 8).

  Next, the volume data synthesizing unit 7 is detected by the position detection unit 11a attached to the ultrasonic probe 4a and the position detection unit 11b attached to the ultrasonic probe 4b and supplied via the main control unit 122 of the system control unit 12. Based on the positional information of the ultrasonic probe 4a and the ultrasonic probe 4b, the first volume data and the second volume data supplied from the volume data generation unit 6 are combined to generate third volume data ( Step S8 in FIG.

  Next, the opacity / color tone setting unit 82 of the image data generation unit 8 sets the transparency and the color tone in units of voxels based on the voxel values of the third volume data, and the rendering processing unit 83 sets the opacity / color tone. Based on the opacity and color tone information set by the unit 82, the third volume data once stored in the volume data storage unit 81 is rendered to generate three-dimensional image data (step S9 in FIG. 8).

  The display data generation unit of the display unit 9 adds incidental information such as subject information supplied from the input unit 10 via the system control unit 12 to the 3D image data generated by the image data generation unit 8. Then, display data is generated, and the data converter performs D / A conversion and display format conversion on the display data and displays the display data on the monitor (step S10 in FIG. 8).

  According to the first embodiment described above, by combining the first volume data generated using the first ultrasonic probe and the second volume data generated using the second ultrasonic probe. High-quality three-dimensional image data in which local sensitivity degradation on image data caused by ultrasonic absorption when the ultrasonic wave propagates through the tissue of the subject or obstacles that prevent this propagation is reduced Can be collected. For this reason, diagnostic accuracy is improved, and when various treatments are performed under observation of the three-dimensional image data, safety in these treatments can be further improved.

  Further, it is possible to emphasize and synthesize effective ultrasonic information by weighted addition of the voxel value of the first volume data and the voxel value of the second volume data as shown in FIG. 3D image data can be collected.

  Next, a second embodiment of the present invention will be described with reference to FIGS. The ultrasonic diagnostic apparatus of the present embodiment includes two ultrasonic probes arranged at different positions of the subject, and first, the first ultrasonic probe sequentially emits the three-dimensional region of the subject. First volume data is generated based on the transmitted ultrasonic wave, and then second volume data is generated based on the transmitted ultrasonic wave emitted from the second ultrasonic probe. Next, the first three-dimensional image data generated by rendering the first volume data and the second three-dimensional image data generated by rendering the second volume data are combined to generate the third 3 Generate dimensional image data.

  That is, the feature of the first embodiment described above is that the first volume data collected by the first ultrasonic probe and the second volume data collected by the second ultrasonic probe are combined to form the third volume data. The volume data is generated and three-dimensional image data for display is generated based on the third volume data. The feature of the present embodiment is that the first ultrasonic probe collects the first volume data. The first three-dimensional image data based on the first volume data and the second three-dimensional image data based on the second volume data collected by the second ultrasonic probe are combined to display three-dimensional image data for display ( (Third 3D image data) is generated.

(Device configuration)
The configuration of the ultrasonic diagnostic apparatus in this embodiment will be described with reference to the block diagram of FIG. However, in FIG. 9, units having substantially the same configuration and function as each unit of the ultrasonic diagnostic apparatus 100 shown in FIG.

  That is, the ultrasonic diagnostic apparatus 200 of the present embodiment shown in FIG. 9 transmits an ultrasonic pulse (transmission ultrasonic wave) to a diagnosis target part of a subject, and an ultrasonic reflected wave (reception ultrasonic wave) obtained by this transmission. Ultrasonic probe 4a (first ultrasonic probe) and ultrasonic probe 4b (second ultrasonic probe) each having a plurality of vibration elements for converting sound waves) into electrical signals (received signals), and ultrasonic probes The probe selection unit 3 that selects the 4a or the ultrasonic probe 4b, and the ultrasonic probe 4a or the ultrasonic wave selected by the probe selection unit 3 as a drive signal for transmitting an ultrasonic pulse in a predetermined direction of the subject. A transmitter / receiver 2 for phasing and adding reception signals of a plurality of channels supplied to the oscillating elements of the probe 4b and obtained from these oscillating elements via the probe selection unit 3, and a reception after phasing addition Three-dimensional ultrasound data obtained by three-dimensional scanning of the subject using the ultrasound data generation unit 5 that performs signal processing on the signal to generate ultrasound data (B-mode data) and the ultrasound probes 4a and 4b. Is provided with a volume data generation unit 6 for generating first volume data and second volume data.

  Furthermore, the ultrasound diagnostic apparatus 100 renders the first volume data and the second volume data to generate first three-dimensional image data and second three-dimensional image data, An image data composition unit 13 for synthesizing the first three-dimensional image data and the second three-dimensional image data to generate third three-dimensional image data, and a display for displaying the obtained third three-dimensional image data Unit 9, input unit 10 for inputting subject information, setting of image data collection conditions, setting of image data display conditions, input of various command signals, and the like, and a position detection unit for detecting position information of ultrasonic probe 4a 11a (first position detection unit), a position detection unit 11b (second position detection unit) that detects position information of the ultrasonic probe 4b, and a system control unit 1 that comprehensively controls each unit described above. It is equipped with a.

(3D image data collection procedure)
Next, a procedure for collecting three-dimensional image data by the ultrasonic diagnostic apparatus 200 having the above-described units will be described with reference to the flowchart of FIG.

  Prior to the ultrasound three-dimensional scanning of the subject, the operator of the ultrasound diagnostic apparatus 200 inputs subject information, sets image data collection conditions, and the like in the input unit 10 (step S11 in FIG. 10). A three-dimensional image data collection start command is input (step S12 in FIG. 10).

  When collecting three-dimensional image data, the probe selection unit 3 connects the vibration elements 41a-1 to 41a-N of the ultrasonic probe 4a and the input / output terminals of the transmission / reception unit 2 according to the selection control signal supplied from the system control unit 12. Connect (step S13 in FIG. 10). Next, the transmitting / receiving unit 2 transmits and receives (θp, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P), φq = φ1 + (q−1) with respect to the central axis of the ultrasonic probe 4a. Ultrasonic wave transmission / reception is sequentially performed with respect to each of Δφ (q = 1 to Q)), and the ultrasonic data generation unit 5 processes the reception signals obtained by the transmission / reception to generate ultrasonic data. Then, the volume data generation unit 6 generates first volume data by interpolating the first three-dimensional ultrasonic data generated by storing the above-described ultrasonic data in correspondence with the transmission / reception direction, The image data generation unit 8 renders the obtained first volume data to generate first three-dimensional image data (step S14 in FIG. 10).

  When the generation of the first three-dimensional image data using the ultrasonic probe 4a is completed, the probe selection unit 3 performs the vibration element 41b-1 to 41b-N of the ultrasonic probe 4b and the transmission / reception unit 2 by the same procedure. Are connected to the input / output terminals (step S15 in FIG. 10). Next, the transmitter / receiver 2 transmits and receives (θp, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P), φq = φ1 + (q−1) with respect to the central axis of the ultrasound probe 4b. Ultrasonic wave transmission / reception is sequentially performed with respect to each of Δφ (q = 1 to Q)), and the ultrasonic data generation unit 5 processes the reception signals obtained by the transmission / reception to generate ultrasonic data.

  Then, the volume data generation unit 6 generates second volume data by interpolating the second three-dimensional ultrasonic data generated by storing the above-described ultrasonic data corresponding to the transmission / reception direction, The image data generation unit 8 renders the obtained second volume data to generate second three-dimensional image data (step S16 in FIG. 10).

  Next, the image data synthesizing unit 13 is detected by the position detecting unit 11a attached to the ultrasonic probe 4a and the position detecting unit 11b attached to the ultrasonic probe 4b, and via the main control unit 122 of the system control unit 12. The first three-dimensional image data and the second three-dimensional image data supplied from the image data generation unit 8 are synthesized based on the positional information of the ultrasonic probe 4a and the ultrasonic probe 4b supplied in the third step. Three-dimensional image data is generated (step S17 in FIG. 10).

  In this case, the first three-dimensional image data and the second three-dimensional image data may be combined based on the method shown in FIG. 5 to generate the third three-dimensional image data, The third 3D image data may be generated by superimposing the first 3D image data and the second 3D image data having different color tones. Further, an image position adjustment unit for finely adjusting the relative position between the first 3D image data and the second 3D image data is newly provided in the input unit 10, and the display unit 9 has third image data as the third image data. The positional deviation in the three-dimensional image data may be corrected under the observation of the displayed first three-dimensional image data and second three-dimensional image data.

  The display data generation unit of the display unit 9 is attached to the third 3D image data generated by the image data synthesis unit 13 such as subject information supplied from the input unit 10 via the system control unit 12. Information is added to generate display data, and the data converter performs D / A conversion and display format conversion on the display data and displays the display data on the monitor (step S18 in FIG. 10).

  According to the second embodiment described above, the first three-dimensional image data generated using the first ultrasonic probe and the second three-dimensional image data generated using the second ultrasonic probe are used. By combining, high-quality images with reduced local sensitivity degradation on the image data caused by ultrasonic absorption when the ultrasound propagates through the tissue of the subject and obstacles that hinder this propagation are reduced. Display three-dimensional image data (third three-dimensional image data) can be obtained. For this reason, the diagnostic accuracy is improved, and when various treatments are performed under the observation of the third three-dimensional image data, the safety in these treatments can be further improved.

  Further, the effective ultrasonic information is emphasized and synthesized by weighted addition of the voxel value of the first three-dimensional image data and the voxel value of the second three-dimensional image data by the same procedure as the method shown in FIG. This makes it possible to collect third 3D image data with excellent diagnostic ability.

  The first embodiment and the second embodiment of the present invention have been described above, but the present invention is not limited to these embodiments, and can be modified. For example, the case where the ultrasonic probe 4a and 4b having a plurality of vibration elements arranged two-dimensionally is used to perform a three-dimensional scan on the diagnosis target part of the subject has been described. Three-dimensional scanning may be performed on the diagnosis target portion by swinging or moving the vibrating element at a high speed in a direction orthogonal to the arrangement direction.

  In the above-described embodiment, the case where the 3D image data is generated using the B mode data as the ultrasonic data has been described. However, the 3D image data or the B mode data based on other ultrasonic data such as color Doppler data It may be 3D image data based on color Doppler data. Furthermore, three-dimensional scanning using the above-described ultrasonic probes 4a and 4b that enable convex scanning, linear scanning, and radial scanning may be used.

  Furthermore, three-dimensional image data for display may be generated by synthesizing three or more volume data or three-dimensional image data collected by three or more ultrasonic probes arranged on the body surface of the subject. Good.

  On the other hand, in the above-described embodiment, the case where volume rendering image data or surface rendering image data is generated as three-dimensional image data has been described. However, the present invention is not limited to this. For example, MIP (Maximum Intensity Projection) images It may be image data reflecting three-dimensional information such as data or MPR (Multi Planar Reconstruction) image data.

  In the above-described embodiment, the transmission / reception direction (θp, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P), φq = φ1 + (q−) with respect to the central axis of the ultrasonic probe 4a. 1) Transmission / reception of ultrasonic waves for each of Δφ (q = 1 to Q)) and transmission / reception directions (θp, φq) (θp = θ1 + (p−1) Δθ (p) with respect to the central axis of the ultrasonic probe 4b = 1 to P), φq = φ1 + (q−1) Δφ (q = 1 to Q)), the case of repeatedly transmitting and receiving ultrasonic waves (see FIG. 7) is shown, but the present invention is not limited to this. Instead, for example, as shown in FIG. 11, the ultrasonic probe 4a and the ultrasonic probe 4b are alternately selected in the transmission / reception cycle (rate cycle) of ultrasonic waves, and transmission / reception is performed with reference to the central axis of the ultrasonic probes 4a and 4b. Direction (θp, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P) , Φq = φ1 + (q−1) Δφ (q = 1 to Q)) may be a transmission / reception method for sequentially transmitting / receiving ultrasonic waves.

  Also, the first volume data collection time and the second volume data collection time in the first embodiment, or the first three-dimensional image data collection time and the second three-dimensional data in the second embodiment. You may control transmission / reception of an ultrasonic wave so that the collection time of image data may differ. In particular, it is possible to obtain display three-dimensional image data with excellent time resolution by setting a short collection time of volume data or three-dimensional image data including ultrasonic information of a fast-moving organ.

  In the above-described embodiment, the center frequency of the transmission ultrasonic wave transmitted from the ultrasonic probe 4a and the center frequency of the transmission ultrasonic wave transmitted from the ultrasonic probe 4b are normally set to be equal. These center frequencies may be set differently. In this case, each of the ultrasonic probe 4a and the ultrasonic probe 4b includes a vibration element having a different resonance frequency, and the drive circuit 213 of the transmission unit 21 has a drive signal having a period corresponding to the resonance frequency of these vibration elements. Is generated. By setting the center frequency of the transmission ultrasonic wave transmitted from the ultrasonic probe 4a and the center frequency of the transmission ultrasonic wave transmitted from the ultrasonic probe 4b to be different, a large amount of biological information depending on the ultrasonic frequency can be obtained. It is possible to combine and display and further improve the diagnostic ability.

  At this time, volume data or three-dimensional image data having a voxel value equal to or higher than a predetermined threshold obtained at one ultrasonic frequency and volume data or three-dimensional image data obtained at another ultrasonic frequency are used. Three-dimensional image data for display may be generated by synthesis.

1 is a block diagram showing the overall configuration of an ultrasonic diagnostic apparatus according to a first embodiment of the present invention. The figure for demonstrating the function of the probe selection part with which the ultrasonic diagnosing device of the Example was equipped. The block diagram which shows the specific structure of the transmission / reception part with which the ultrasonic diagnostic apparatus of the Example was provided, and the ultrasonic data generation part. The figure which shows the ultrasonic transmission / reception direction on the basis of the central axis of the ultrasonic probe in the Example. The figure for demonstrating the synthetic | combination method of the volume data in the Example. The block diagram which shows the specific structure of the image data generation part with which the ultrasonic diagnosing device of the Example was equipped. The figure for demonstrating selection control of the ultrasonic probe in the Example, and switching control of the transmission / reception direction with respect to these ultrasonic probes. The flowchart which shows the collection procedure of the three-dimensional image data in the Example. The block diagram which shows the whole structure of the ultrasonic diagnosing device in the 2nd Example of this invention. The flowchart which shows the collection procedure of the three-dimensional image data in the Example. The figure for demonstrating the selection control of the ultrasonic probe in the modification of the 1st Example of this invention, and the 2nd Example, and the switching control of the transmission / reception direction with respect to these ultrasonic probes.

Explanation of symbols

2. Transmission / reception unit 21 ... Transmission unit 211 ... Rate pulse generator 212 ... Transmission delay circuit 213 ... Drive circuit 22 ... Reception unit 220 ... Preamplifier 221 ... A / D converter 222 ... Reception delay circuit 223 ... Adder 3 ... Probe selection 4a, 4b ... ultrasonic probe 5 ... ultrasonic data generation unit 51 ... envelope detector 52 ... logarithmic converter 6 ... volume data generation unit 7 ... volume data synthesis unit 8 ... image data generation unit 81 ... volume data storage unit 82 ... Opacity / color tone setting unit 83 ... Rendering processing unit 84 ... Three-dimensional image data storage unit 9 ... Display unit 10 ... Input unit 11a, 11b ... Position detection unit 12 ... System control unit 121 ... Scan control unit 122 ... Main control Unit 13 ... Image data synthesis unit 100, 200 ... Ultrasonic diagnostic apparatus

Claims (10)

In an ultrasonic diagnostic apparatus that generates image data based on volume data obtained by three-dimensional scanning of ultrasonic waves on a subject,
A plurality of ultrasonic probes for performing the three-dimensional scanning from a plurality of different directions of the subject;
Position detecting means for detecting position information of the ultrasonic probe;
Volume data generating means for generating a plurality of volume data based on reception signals collected by three-dimensional scanning on the subject using each of the plurality of ultrasonic probes;
Volume data synthesizing means for synthesizing the plurality of volume data based on position information of the ultrasonic probe;
Image data generating means for processing the combined volume data to generate image data;
An ultrasonic diagnostic apparatus comprising: display means for displaying the image data.   The volume data synthesizing means includes a voxel value at a predetermined position in each of the plurality of volume data aligned based on position information of the ultrasonic probe, an ultrasonic probe used to generate the volume data, the predetermined position, The ultrasonic diagnostic apparatus according to claim 1, wherein a voxel value at the predetermined position in the synthesized volume data is set by a weighting process based on a distance between the ultrasound diagnosis apparatus and the synthesized volume data. In an ultrasonic diagnostic apparatus that generates image data based on volume data obtained by three-dimensional scanning of ultrasonic waves on a subject,
A plurality of ultrasonic probes for performing the three-dimensional scanning from a plurality of different directions of the subject;
Position detecting means for detecting position information of the ultrasonic probe;
Volume data generating means for generating a plurality of volume data based on reception signals collected by three-dimensional scanning on the subject using each of the plurality of ultrasonic probes;
Image data generating means for processing each of the plurality of volume data to generate a plurality of image data;
Image data synthesizing means for synthesizing the plurality of image data based on position information of the ultrasonic probe;
An ultrasonic diagnostic apparatus comprising: display means for displaying the synthesized image data.   The image data synthesizing means includes a pixel value at a predetermined position in each of the plurality of image data aligned based on position information of the ultrasonic probe, the ultrasonic probe used to generate the image data, the predetermined position, 4. The ultrasonic diagnostic apparatus according to claim 3, wherein a pixel value at the predetermined position in the combined image data is set by a weighting process based on the distance.   The ultrasonic diagnostic apparatus according to claim 3, wherein the image data synthesizing unit synthesizes the plurality of image data by adding different color information.   4. The ultrasonic diagnosis according to claim 1, further comprising probe selection means, wherein the probe selection means sequentially selects the plurality of ultrasonic probes at an image data generation interval or an ultrasonic transmission / reception interval. apparatus.   The ultrasonic diagnostic apparatus according to claim 1, wherein the position detection unit detects position information of the ultrasonic probe by a magnetic sensor method or an ultrasonic sensor method.   The ultrasonic diagnostic apparatus according to claim 1, wherein the image data generation unit generates volume rendering image data or surface rendering image data by rendering the volume data.   The ultrasonic diagnostic apparatus according to claim 1, wherein the image data generation unit generates MIP image data or MPR image data using the volume data.   4. The ultrasonic diagnostic apparatus according to claim 1, wherein each of the plurality of ultrasonic probes transmits and receives an ultrasonic pulse having a different center frequency to and from the subject.

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