JP5159326B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus that transmits a low frequency to stimulate a muscle to exercise, and transmits and receives ultrasonic waves to the moving muscle to visualize the movement of the muscle.

  In order to quantify the movement of a tissue such as muscle, it is common to measure using a measuring instrument such as a grip strength meter. With such a measuring instrument, it is possible to comprehensively quantify the muscles being exercised, but it is difficult to quantify each muscle fiber one by one.

  For this reason, currently, a method has been presented in which an ultrasonic diagnostic apparatus captures muscle motion as an image or video and quantifies the muscle motion based on the image or video.

  An ultrasonic diagnostic apparatus is an apparatus that transmits an ultrasonic wave into a living body, receives a reflected wave from the living body, and images or visualizes a structure in the living body from the intensity and reflection position of the reflected wave. . Methods for quantifying the movement of tissues such as muscles include the Doppler method and two-dimensional tracking method, all of which capture the movement of each point of muscle from images and images based on the transmission and reception of ultrasonic waves. The degree of distortion indicated by the movement amount, movement speed, acceleration, and the like of each point in time phase is calculated (see, for example, “Patent Document 1”).

  With this ultrasonic transmission / reception and quantification methods such as Doppler method and two-dimensional tracking method, it became possible to quantify the movement of each muscle fiber. There are problems due to the necessity. When the subject exercises the muscles consciously, the movement of the muscles cannot be stably imaged or visualized due to factors such as physical condition, environment, physical strength, etc. You can only get results. In particular, when the muscle cannot be consciously exercised due to pathology or the like, it is difficult to image or even image the movement of the muscle.

JP 2007-236606 A

  The present invention has been made in view of the above circumstances, and an object of the present invention is to image or visualize a muscle that moves stably by moving the muscle regardless of the consciousness of the subject. It is to provide an ultrasonic diagnostic apparatus.

In order to solve the above-described problems, an ultrasonic diagnostic apparatus according to the present invention includes an ultrasonic probe having an ultrasonic wave transmission / reception surface in a head, and the ultrasonic probe interposed between the heads, so that a low-frequency pulse is generated. An image processing means for generating an image of the living body based on a reflected wave received from the electrically stimulated living body by the ultrasonic probe; Display means for displaying, strain measurement means for measuring a value indicating strain of the living body due to the electrical stimulation based on the image, and sticking that is arranged along an edge of the head and is stuck to the living body The positive electrode and the negative electrode are scattered and arranged on the surface of the sticking part that sticks to the living body .

Bei example a pair of puncture needles disposed in the ultrasonic probe across the head, the positive electrode and the negative electrode, the invention of the may also be housed in the puncture needle (claim 2, wherein Equivalent).

The positive electrode and the negative electrode are arranged in a row with the counter electrodes facing each other, and each positive side switch corresponding to each of the plurality of positive electrodes and each negative side corresponding to each of the plurality of negative electrodes A switch, and a low-frequency current control unit that selectively switches on and off the positive-side switch and the negative-side switch independently may be provided (corresponding to the invention according to claim 3 ).

The low-frequency current control means turns on the positive side switch and the negative side switch corresponding to the positive electrode and the negative electrode that are not opposed to each other, so that the low frequency current control unit is inclined with respect to the direction in which the positive electrode and the negative electrode are arranged Alternatively, a low-frequency current directed to the power source may be transmitted (corresponding to the invention described in claim 4 ).

The low frequency current control means transmits a low frequency current to a predetermined width of the living body by turning on the positive side switch and the negative side switch corresponding to the plurality of adjacent positive electrodes and negative electrodes. You may make it make it (equivalent to invention of Claim 5 ).

The display means displays the positive electrode to which the pulse is applied and the negative electrode so as to be individually selectable, and the low frequency current control means corresponds to the positive electrode and the negative electrode selected based on the display. The positive electrode side switch and the negative electrode side switch may be turned on (corresponding to the invention of claim 6 ).

A development frequency for evaluating the development of the living body based on the value indicating the distortion is stored in advance as a comparison target, and the development frequency based on the value indicating the measured distortion is stored in advance as the comparison target. You may make it further provide the development comparison part which displays the development frequency simultaneously on the said display means (equivalent to the invention of Claim 7 ).

A general value indicating the distortion for each age is stored in advance, and based on the predicted increase / decrease rate of the distortion after a predetermined number of years from the age of the subject based on the general value, and the value indicating the measured distortion, You may make it further provide the development prediction means which calculates the predicted value of the distortion | strain of the said biological body after the said predetermined years (equivalent to the invention of Claim 8 ).

  Depending on the aspect of the present invention, since it has a mechanism for exercising muscles regardless of consciousness by transmitting low frequency, imaging of stable muscular motion, including the case where the muscles cannot be moved consciously due to pathology or the like, Can be visualized. Further, by imaging or imaging this stable muscle movement, it is possible to sample the degree of muscle distortion that is not influenced by the environment or physical condition, and it is possible to make a highly accurate comparison and development prediction.

  Hereinafter, preferred embodiments of an ultrasonic diagnostic apparatus according to the present invention will be specifically described with reference to the drawings.

  First, an ultrasonic diagnostic apparatus is an apparatus that transmits and receives an ultrasonic wave and generates an image or a video based on the intensity and reflected position of a reflected wave. This ultrasonic diagnostic apparatus has an ultrasonic probe that transmits and receives ultrasonic waves.

  1 to 3 are diagrams showing the configuration of the ultrasonic probe according to the present embodiment. 1A and 1B are schematic views showing the appearance of an ultrasonic probe 1a with a low-frequency transmission mechanism according to a first specific example, where FIG. 1A is a side view and FIG. 1B is a front view as viewed from the head 11 side. It is. FIG. 2 is a schematic diagram showing an appearance of an ultrasonic probe 1b with a low-frequency transmission mechanism according to a second specific example, and FIG. 3 is a block diagram showing an internal configuration of the ultrasonic probe 1b with a low-frequency transmission mechanism. is there. Hereinafter, when the ultrasonic probe 1a with a low frequency transmission mechanism and the ultrasonic probe 1b with a low frequency transmission mechanism are not distinguished from each other, they are simply referred to as the ultrasonic probe 1 with a low frequency transmission mechanism.

  The ultrasonic probe 1 with a low-frequency transmission mechanism has an ultrasonic wave transmission / reception surface on a head 11. In the head 11, a plurality of piezoelectric elements are arranged in a one-dimensional shape or a two-dimensional shape. By applying a signal voltage to this piezoelectric element, ultrasonic waves are transmitted from the head 11 side of the ultrasonic probe 1 with a low-frequency transmission mechanism. Further, when the piezoelectric element receives the reflected wave, an echo signal corresponding to the intensity of the reflected wave is output.

The piezoelectric element is composed of a ceramic material such as lead zirconate titanate Pb (Zr, Ti) O ₃ , lithium niobate (LiNbO ₃ ), barium titanate (BaTiO ₃ ), or lead titanate (PbTiO ₃ ). Yes. This piezoelectric element is an acoustic / electric reversible conversion element. When a signal voltage is applied, an ultrasonic wave is oscillated by a piezoelectric effect, and when an ultrasonic wave is received, an echo signal is output according to the intensity of the ultrasonic wave. .

  As shown in FIG. 1, a bonding pad 12 is disposed along an edge of a head 11 in which a piezoelectric element is included in an ultrasonic probe 1a with a low-frequency transmission mechanism according to a first specific example. The front surface of the sticking pad 12 has adhesiveness. Further, the adhesive pad 12 is dotted with a plurality of negative electrodes 15 and positive electrodes 14 through which a low-frequency current is conducted. The negative electrode 15 and the positive electrode 14 are arranged to face each other with the head 11 interposed therebetween. The negative electrode 15 and the positive electrode 14 are connected to a lead wire 16 (not shown) for energizing each. The lead wire 16 is connected to a controller 100 of the ultrasonic diagnostic apparatus main body 2 described later via a cord 17.

  As shown in FIG. 2, the ultrasonic probe 1b with a low-frequency transmission mechanism according to the second specific example is paired so that the head 11 is sandwiched between opposite side surfaces of the head 11 including the piezoelectric element. The puncture needle 13 is arranged. The puncture needle 13 passes through the flanges provided upright on both side surfaces behind the head 11 and is supported so as to have an axis in a direction substantially the same as the direction in which the front surface of the head 11 faces. A lead wire 16 extending from the inside of the cord 17 is drawn out from the flange. The lead wire 16 extends from the end opposite to the head 11 of the puncture needle 13 into the puncture needle 13.

  As shown in FIG. 3, inside the puncture needle 13, a plurality of positive electrodes 14 are arranged on one puncture needle 13 along the axis, and a plurality of negative electrodes 15 are arranged on the other puncture needle 13 along the axis. Contained. The positive electrode 14 and the negative electrode 15 are arranged so that the counter electrode exists at the same height when one end of the puncture needle 13 is aligned. In other words, the counter electrodes are arranged so as to face each other. The lead wire 16 is connected to the positive electrode 14 and the negative electrode 15.

  In such an ultrasonic probe 1 with a low frequency transmission mechanism, when a low frequency pulse is applied to a pair of the negative electrode 15 and the positive electrode 14, the negative electrode 15 and the positive electrode 14 to which the pulse is applied are energized. As a result, a low-frequency current flows in the meantime. The positive electrode 14 and the negative electrode 15 to which the pulse is applied are individually and selectively switched by a switch.

  FIG. 4 is a diagram showing a configuration for switching between the positive electrode 14 and the negative electrode 15 to which the pulse is applied.

  As shown in FIG. 4, a switch 18 such as a gate circuit is individually connected to each positive electrode 14 and each negative electrode 15. As will be described later, this switch is arranged in the low-frequency pulse signal transmission unit 3 and is switched by on / off control of the low-frequency current control unit 110 of the controller 100. When any switch 18 corresponding to each positive electrode 14 and any switch 18 corresponding to each negative electrode 15 are turned on, pulses are applied to the positive electrode 14 and the negative electrode 15 connected to the turned-on switch 18. Is applied while a low frequency current flows.

  The switch 18 to be turned on may correspond to the positive electrode 14 and the negative electrode 15 facing each other, or may correspond to the positive electrode 14 and the negative electrode 15 that are not opposed to each other. That is, on / off of the positive electrode 14 and the negative electrode 15 is switched individually, in other words, independently. By selecting the switch 18 to be turned on separately on the positive electrode 14 side and the negative electrode 15 side, various directivities are given to the transmitted current.

  Further, the switch 18 to be turned on may correspond to not only a pair but also a plurality of pairs of the positive electrode 14 and the negative electrode 15. By turning on a switch 18 corresponding to a plurality of adjacent positive electrodes 14 and negative electrodes 15, a current is transmitted to the muscle with the arrangement width of the positive electrodes 14 and negative electrodes 15 corresponding to the turned-on switches 18. be able to.

  5 and 6 are schematic views showing an example of mounting the ultrasonic probe 1 with a low-frequency transmission mechanism on a subject. FIG. 5 shows a mounting example of the ultrasonic probe 1a with a low-frequency transmission mechanism, and FIG. 6 shows a mounting example of the ultrasonic probe 1b with a low-frequency transmission mechanism.

  As shown in FIG. 5, the ultrasonic probe 1a with a low-frequency transmission mechanism contacts the body surface with the head 11 facing a living body, for example, a muscle, whose motion is to be imaged, and the muscle is connected to each negative electrode 15 and each positive electrode. The sticking pad 12 is stuck and used so that the electrode 14 is surrounded from the surroundings.

  Further, as shown in FIG. 6, the ultrasonic probe 1b with a low-frequency transmission mechanism contacts the body surface with the head 11 facing a living body, for example, a muscle, whose motion is to be imaged. The puncture needle 13 is inserted into the body so as to sandwich the muscle.

  By mounting such an ultrasonic probe 1a or 1b with a low-frequency transmission mechanism, a muscle whose motion is to be imaged is sandwiched between the negative electrode 15 and the positive electrode 14, and the negative electrode 15 and the positive electrode 14 are energized. The muscle is stimulated with a low frequency current and forced to exercise. Then, an ultrasonic wave is transmitted from the transmission / reception surface of the head 11 to the muscle forced to exercise, and the reflected wave reflected from the muscle is received, so that the muscle forced to exercise is imaged or Visualized. Visualization means that images are continuously generated at different times.

  The ultrasonic probe 1 with a low frequency transmission mechanism is connected to the ultrasonic diagnostic apparatus main body 2 via a cord 17. Then, a signal voltage for ultrasonic transmission is applied from the ultrasonic diagnostic apparatus main body 2 with a delay for each piezoelectric element. Further, a signal voltage for applying a low-frequency current from the ultrasonic diagnostic apparatus main body 2 is applied to the pair or plural pairs of the positive electrode 14 and the negative electrode 15 simultaneously or delayed. The echo signal output from the ultrasonic probe 1 with a low-frequency transmission mechanism is input to the ultrasonic diagnostic apparatus body 2. The ultrasonic diagnostic apparatus main body 2 processes this echo signal to image or image the muscle movement.

  FIG. 7 is a block diagram showing a configuration of the ultrasonic diagnostic apparatus main body 2.

  The ultrasonic diagnostic apparatus body 2 includes an ultrasonic pulse signal transmitter 4, a low frequency pulse signal transmitter 3, a receiver 5, a B / M processor 61, a CFM processor 62, a DSC 7 (Digital Scan Converter), and a video. An I / F 8, a monitor 9, a controller 100, and a console 120 are provided. The ultrasonic pulse signal transmission unit 4, the low frequency pulse signal transmission unit 3, and the reception unit 5 are electrically connected to the ultrasonic probe 1 with a low frequency transmission mechanism via a signal line. Also, the receiving unit 5 and the B / M processing unit 61, the receiving unit 5 and the CFM processing unit 62, the B / M processing unit 61 and the DSC 7, the CFM processing unit 62 and the DSC 7, the DSC 7 and the video I / F 8, and the video I / F 8 A monitor 9 is electrically connected. Moreover, the controller 100 and each component are electrically connected so that control is possible.

  The ultrasonic pulse signal transmission unit 4 generates a pulse signal having a frequency belonging to an ultrasonic wave, and applies the pulse signal to the piezoelectric element of the ultrasonic probe 1 with a low-frequency transmission mechanism. The transmission unit includes a pulse generator 41, a delay circuit 42, and a high output circuit 43.

  The pulse generator 41 is a circuit that generates a pulse signal. An internal clock generator for generating a basic signal is provided, and a pulse signal having a frequency represented by preset frequency data is output based on the frequency of the basic signal. The frequency of the ultrasonic wave transmitted by the pulse generator 41 is determined.

  The delay circuit 42 is a circuit that delays the pulse signal generated by the pulse generator 41 for each piezoelectric element. For each piezoelectric element, an ultrasonic wave is focused on the beam and a delay time necessary for determining the transmission directivity is given to each pulse signal.

  The high output circuit 43 applies a signal voltage to each piezoelectric element in accordance with a pulse signal for each piezoelectric element that has been delayed.

  In a specific example of measuring the degree of muscle distortion described later, for example, B-mode imaging and tissue Doppler mode imaging need to be executed in parallel. In such a specific example, the transmission unit forms a transmission waveform under the control of the controller 100 so as to execute, for example, several B-mode transmissions and several subsequent Doppler transmissions for each scanning line.

  The low-frequency pulse signal transmitter 3 generates a low-frequency pulse signal and selectively applies it to any one or a plurality of pairs of the negative electrode 15 and the positive electrode 14 of the ultrasonic probe 1 with a low-frequency transmission mechanism. . The low-frequency pulse signal transmission unit 3 includes a switch 18 for each negative electrode 15 and each positive electrode 14. The on / off control of the switch 18 is controlled by a controller 100 described later.

  The receiving unit 5 receives an echo signal output from the ultrasonic probe 1 with a low-frequency transmission mechanism. The receiving unit 5 amplifies the echo signal and converts it into a digital signal. Furthermore, a delay time necessary to determine the reception directivity is given to the echo signal output from each piezoelectric element, and phasing addition is performed, and a single echo in which the reflection component from the direction corresponding to the reception directivity is emphasized. Generate a signal. The receiving unit 5 outputs the processed echo signal to the B / M processing unit 61 and the CFM processing unit 62.

  The B / M processing unit 61 attenuates a reflected wave component in a predetermined frequency band, performs a band-pass filter process for extracting a reflected wave component in a desired frequency band, and then performs envelope detection to perform the envelope detection. Detect ingredients. Thereafter, the B / M processing unit 61 performs logarithmic compression processing and, if necessary, edge enhancement processing on the echo signal. The B / M processing unit 61 outputs the signal sequence generated by the processing to the DSC 7.

  The CFM processing unit 62 performs high-pass filter processing (also referred to as “MTI filter processing” or “Wall filter processing”) for separating an echo signal into a tissue signal and a blood flow signal, and the movement speed of the tissue or blood flow. An autocorrelation process for detection is executed. Further, the CFM processing unit 62 performs non-linear processing for reducing / deleting the tissue signal in the echo signal as necessary. The CFM processing unit 62 outputs the signal sequence generated by the processing to the DSC 7.

  The DSC 7 is a digital scan converter, which generates an ultrasonic image by mapping the signal sequence input from the B / M processing unit 61 and the CFM processing unit 62 to a position corresponding to transmission / reception of an ultrasonic beam, and is orthogonal Convert. The ultrasonic raster data includes an angle θ between the projected trajectory of the ultrasonic beam on the XY plane and the Y axis and the distance K between the position of the ultrasonic probe 1 with the low-frequency transmission mechanism and the sampling point. It is obtained in the coordinate system represented by An ultrasonic image obtained in this coordinate system is orthogonally transformed into a coordinate system (X, Y) of display image data. The B-mode ultrasound image and the CFM-mode ultrasound image generated by the DSC 7 are output to the video I / F 8.

  The video I / F 8 combines various information related to the B-mode ultrasound image, the CFM-mode ultrasound image, and other ultrasound images with each image to form a display image laid out for the monitor 9 display. 9 displays the display image. The monitor 9 is a device having a screen such as an LCD (Liquid Crystal Display) display or a CRT (Cathode Ray Tube) display.

  The controller 100 includes a CPU 101 and a memory 102, and statically or dynamically controls the ultrasonic diagnostic apparatus main body 2 as a control center of the entire system. Under the control of the controller 100, the echo signal and the ultrasonic image are subjected to various processes in each configuration, sent to the next-stage configuration, and stored in the memory 102.

  The ultrasonic wave transmission / reception process and the ultrasonic image generation process are started when the ultrasonic wave transmission / reception button displayed on the monitor 9 is pressed. The controller 100 displays a patient information display screen on the monitor 9 in advance, and arranges ultrasonic transmission / reception buttons on this screen. The patient information display screen is a screen that displays information on a subject to be imaged by ultrasonic wave transmission / reception. When information identifying the subject such as the nationality, gender, age, and patient ID or patient name of the subject is input using the console 120, the controller 100 sets the information identifying the entered subject. The information is stored in the memory 102 and further displayed on the patient information display screen of the monitor 9.

  In addition, the controller 100 executes a low-frequency transmission direction control process, a muscle distortion degree measurement process, a distortion degree comparison process, and a future muscle growth prediction process, which will be described later. More specifically, the CPU 101 decodes and executes a program stored in the memory 102 to execute each of these processes. However, the present invention is not limited to this, and each of these processes may be executed by a hardware configuration.

  The controller 100 performs control processing of the low frequency transmission direction, measurement processing of the degree of distortion of the muscle, comparison processing of the degree of distortion, and processing for predicting the future development of the muscle, triggered by an operation using the console 120. It executes based on the input using the console 120. The console 120 is a keyboard, a mouse, or a trackball.

  FIG. 8 is a block diagram showing a more detailed configuration of the controller 100 that executes each of the processes described above. FIG. 3 is a functional block diagram showing functions of a controller 100 when each of the above processes is executed by decoding and executing a program.

  The controller 100 controls each part related to ultrasonic image generation of the ultrasonic diagnostic apparatus main body 2, and also includes a low frequency current control unit 110, a strain measurement unit 111, a development comparison unit 112, and a development prediction processing unit 113. Have

  The low frequency current control unit 110 receives the transmission directivity of the low frequency current transmitted from the sticking pad 12 or the puncture needle 13 included in the ultrasonic probe 1 with the low frequency transmission mechanism and the current flowing range. The low-frequency current control unit 110 receives this input and outputs a signal for turning on the switch 18 of the positive electrode 14 and the negative electrode 15 through which a low-frequency current flows.

  The distortion measuring unit 111 measures the degree of distortion of the muscles that appear in the frames of the ultrasonic images from the two frames of ultrasonic images arranged in front and back in time series. The degree of strain is a value indicating the strain of the muscle, and is represented by the speed or acceleration or the amount of stretch at each point of the muscle.

  The development comparison unit 112 creates the development frequency and displays it on the monitor 9 along with the comparison target. The degree of development is a value for evaluating muscle development based on the degree of distortion of each measured sample point. This degree of development is represented by the division to which the measured distortion degree of each sample point belongs and the ratio of the sample points belonging to that division. The development comparison unit 112 creates the development frequency based on each distortion level measured by the strain measurement unit 111, creates a comparison table in which the development frequency is arranged as a comparison target, and displays the comparison table on the monitor 9.

  The development prediction processing unit 113 calculates a predicted value after a predetermined number of years from the measured degree of distortion and the transition of the sampled general value for each age. For this calculation, an average distortion degree is used. The average degree of distortion is a value calculated by averaging the degree of distortion at each measured point. The general value is obtained by further averaging the average distortion degree of the sampled constant parameter. After a predetermined number of years, for example, one year later.

  First, the control process of the low frequency transmission direction by the low frequency current control part 110 among each structure regarding the above-mentioned controller 100 is demonstrated.

  The low frequency current control unit 110 outputs a signal for turning on the switch 18 corresponding to the positive electrode 14 and the negative electrode 15 to which the pulse signal is applied, to the low frequency pulse signal transmission unit 3. The transmission directivity and range of the low-frequency current are input using the console 120. The low frequency current control unit 110 outputs a signal for turning on the switch 18 corresponding to the positive electrode 14 and the negative electrode 15 instructed by the input operation to the low frequency pulse signal transmission unit 3.

  The low frequency current control unit 110 causes the monitor 9 to display a screen that supports an operation for inputting the transmission directivity and range of the low frequency current.

  FIG. 9 is a schematic diagram showing a screen that supports an operation for inputting the transmission directivity and range when the ultrasonic probe 1 a with a low-frequency transmission mechanism according to the first specific example is connected to the ultrasonic diagnostic apparatus main body 2. FIG. The monitor 9 includes a first image 91 showing a front view seen from the head 11 side of the ultrasonic probe 1a with a low-frequency transmission mechanism, an ultrasonic image currently taken, and a positive electrode on the ultrasonic image. 14 and an electrode mark 93 indicating the position of the negative electrode 15 are displayed side by side on a screen along with a second image 92 showing a combination of the two. In this front view, electrode marks 93 indicating the positions of the positive electrode 14 and the negative electrode 15 arranged around the head 11 are displayed.

  FIG. 10 shows a screen that supports an operation for inputting the transmission directivity and range when the ultrasonic probe 1b with a low-frequency transmission mechanism according to the second specific example is connected to the ultrasonic diagnostic apparatus body 2. It is a schematic diagram shown. The monitor 9 includes an ultrasonic image currently being photographed, a puncture needle 13 mark 96 indicating the position of the puncture needle 13 on the ultrasonic image, and an electrode mark 93 indicating the positions of the positive electrode 14 and the negative electrode 15. A second image 92 in which is combined is displayed.

  While the screen of FIG. 9 or 10 is displayed, if the operation of pressing the electrode mark 93 for selecting a pair or a plurality of pairs of the positive electrode 14 and the negative electrode 15 using the console 120 is performed, the low frequency The current control unit 110 causes the monitor 9 to display a low-frequency transmission direction mark 94 such as an arrow on a line connecting the electrode marks 93 indicating the selected positive electrode 14 and negative electrode 15. The input to be selected is, for example, a movement of the cursor 95 movable on the screen onto the electrode mark 93 and a selection operation such as a click.

  When an input operation for selecting one or more of the positive electrode 14 and the negative electrode 15 is performed using the console 120 and the confirmation button is pressed, the low frequency current control unit 110 selects the positive electrode 14 and the negative electrode selected. A signal indicating the electrode 15 is output to the low-frequency pulse signal transmitter 3.

  FIG. 11 is a schematic diagram showing a first specific example in which a pulse signal is applied to the positive electrode 14 and the negative electrode 15 arranged in the ultrasonic probe 1b with a low-frequency transmission mechanism according to the second specific example.

  As shown in FIG. 11, when the low-frequency current control unit 110 turns on the switch 18 corresponding to one positive electrode 14 and the negative electrode 15 facing the positive electrode 14, the positive electrode 14 and the negative electrode 15 are arranged. A low frequency current flows along the same depth. Further, when a switch 18 corresponding to a plurality of adjacent positive electrodes 14 and a negative electrode 15 opposed thereto is turned on, a depth width (D in the figure) in which the positive electrodes 14 and the negative electrodes 15 that are energized are arranged. Low frequency current flows through

  FIG. 12 is a schematic diagram showing a second specific example in which a pulse signal is applied to the positive electrode 14 and the negative electrode 15 arranged in the ultrasonic probe 1b with a low-frequency transmission mechanism.

  As shown in FIG. 12, when the switch 18 corresponding to one positive electrode 14 and the negative electrode 15 arranged at a different depth from the positive electrode 14 is turned on, the positive electrodes 14 having different energized depths are turned on. A low frequency current flows between the negative electrode 15 and the negative electrode 15. That is, a low frequency current flows in an oblique direction.

  FIG. 13 is a schematic diagram showing a third specific example in which a pulse signal is applied to the positive electrode 14 and the negative electrode 15 arranged in the ultrasonic probe 1b with a low-frequency transmission mechanism.

  As shown in FIG. 13, when a switch 18 corresponding to a plurality of adjacent positive electrodes 14 and a plurality of adjacent negative electrodes 15 arranged at different depths from these positive electrodes 14 is turned on, this energization is performed. A low-frequency current flows in an oblique direction with the arrangement width (D in the figure) of the positive electrode 14 and the negative electrode 15.

  In the case where the current flows in the oblique direction and with a width including a plurality of electrodes, the low frequency current control unit 110 applies a pulse signal with a time delay in order to the electrodes. For example, among the selected positive electrode 14 and negative electrode 15, the switch 18 corresponding to the shallowest pair is turned on, and then the switch 18 for the shallowest pair is turned off, and then the switch 18 for the pair immediately below it. Turn on. This is because if a pulse voltage is applied at the same time, a voltage flows between the shortest electrode and current may not flow in an oblique direction. The delay interval is preferably shorter than the frame rate for generating the ultrasonic image.

  In the ultrasonic probe 1a with a low-frequency transmission mechanism, a pair of a positive electrode 14 and a negative electrode 15 to which a pulse signal is applied is selected in the same manner, so that a low frequency can be generated in an oblique direction on the body surface. Make a call.

  The arrangement and arrangement of the negative electrode 15 and the positive electrode 14 of the ultrasonic probe 1 with the low-frequency transmission mechanism and the individual selection control of the negative electrode 15 and the positive electrode 14 to which a pulse signal is applied, the width and transmission for transmitting a low frequency. Directivity becomes free, and a low frequency suitable for the muscle fiber direction and muscle fiber width of the muscle for which the motion is to be imaged or imaged can be transmitted.

  Next, a distortion degree measurement process by the distortion measurement unit 111 will be described. FIG. 14 is a flowchart showing a distortion degree measurement process by the distortion measurement unit 111.

  First, the distortion measurement unit 111 uses the front and back frames of the B-mode ultrasound image output from the B / M processing unit 61 and generated by mapping by the DSC 7 to move the tracking points sampled roughly. The movement vector relating to each point is obtained by estimation using the dimension tracking method (step S1).

  In this step S1, a rough sample point is set as a tracking point in an ultrasonic image of one frame, and its movement is detected by a two-dimensional tracking method using an ultrasonic image of a previous or subsequent frame. Estimate and determine the movement vector for each point.

  Here, the setting of the sample points is realized, for example, by setting a grid-like marker with an interval of 3 mm on the ultrasonic image of one frame and using the data at the position corresponding to the intersection of the grids as the sample points. be able to. As the two-dimensional tracking, for example, a cross correlation method is adopted.

The cross-correlation function R (x ′, y ′) is defined by the following equation (1), for example.
R (x ′, y ′) = ∫∫ [f (x + x ′, y + y ′) · g (x, y)] dxdy (1)
Here, g (x, y) is a function representing a predetermined area in the image, and f (x, y) is a function representing a predetermined area in the image for the next time phase of the image.

  (X ′, y ′) that maximizes the value of this cross-correlation function R (x ′, y ′) is most correlated (similarity) with f (x, y) in the next time phase ultrasound image. It can be estimated that this is a moving region. By performing this estimation for all the roughly sampled tracking points (or a region including the tracking points), each tracking point can be tracked.

  The magnitude of the movement vector is defined by the movement amount of each sample point, and the vector direction is defined by the movement direction of each sample point. Since the movement amount and movement direction of each sample point can be obtained by the tracking, the movement vector for each sample point is defined by these two physical quantities.

  The amount of movement indicated by this movement vector is the amount of elongation at the sample point of the muscle. By dividing this movement amount by the time difference between frames, the speed of muscle extension or contraction at the sample point is obtained. Further, the acceleration of muscle extension or contraction is obtained by dividing the speed of extension or contraction by the time difference between frames.

In addition, as a cross-correlation function, the structure which employ | adopts the cross-correlation function R (x ', y') about the least squares defined, for example by following Formula (2) may be sufficient.
R (x ′, y ′) = ∫∫ [f (x + x ′, y + y ′) − g (x, y)] ² dxdy (2)

  Next, the distortion measurement unit 111 obtains a movement vector related to a finer sample point by interpolation processing (step S2).

  In step S2, a movement vector related to a finer sample point is obtained by interpolation processing. Note that a finer sample point means, for example, a sample point for all pixels in this embodiment.

  Fine sample points by interpolation processing can be obtained by executing interpolation processing such as linear interpolation on the x-coordinate and y-coordinate of each sample point based on the movement vector relating to the coarse sample point obtained in step S1. .

  When the degree of distortion is indicated by an elongation amount, it is obtained by steps S1 and S2 for calculating the movement amount of the movement vector at each sample point.

  Next, in the case where the degree of distortion is expressed by the speed or acceleration of expansion or contraction, the distortion measurement unit 111 uses the angle between the scanning vector and the scanning line obtained in step S2 for all pixels, and performs tissue Doppler. The angle value of the separately acquired speed value is corrected to obtain a corrected speed (step S3).

  In this step S3, using the angle between the scanning vector of each sample point obtained in step S2 and the scanning line, a super image which is an image of a tissue Doppler output from the CFM processing unit 62 and mapped by the DSC 7 is obtained. The speed value of each point corresponding to the sample point of the sound wave image is angle-corrected to obtain a corrected speed. This angle correction is executed according to the following equation (3).

(Speed after correction) = (Speed obtained by tissue Doppler method) / cos θ (3)
Here, θ (Doppler angle) is an angle formed between the moving direction obtained by two-dimensional tracking and the scanning line.

  When the degree of distortion is expressed by the speed of expansion or contraction, the distortion measurement unit 111 acquires this correction speed as the degree of distortion at each sample point. Also, when the degree of distortion is expressed by acceleration of expansion or contraction, the distortion measurement unit 111 divides the correction speed by the time difference between frames.

  The angle correction in step S3 becomes less reliable as the Doppler angle θ increases. Therefore, in the present embodiment, it is preferable from the viewpoint of accuracy to prioritize the movement amount based on the movement vector obtained in step S2 over the movement amount based on the correction speed as the Doppler angle θ increases.

That is, the amount of movement D _dop obtained by correcting the speed by the correction of the Doppler velocity of the step _S3, when the movement amount obtained by the tracking of the steps S1 and S2 and D _track the movement of the movement vector, for example, by the following equation (4) The quantity D _sec can be redefined.
D _sec = f (θ) · D _dop + (1−f (θ)) · D _track (4)
Here, f (θ) is a function that satisfies 0 ≦ f (θ) ≦ 1 where θ increases as it moves away from 90 degrees and decreases as it approaches 90 degrees.

  The degree of distortion measured by this processing is stored in the memory 102 together with information identifying the subject's nationality, gender, age, and subject stored in the memory 102 in advance. The strain gauge side identifies the subject's nationality, gender, age, and subject, using the console 120 to input the measured distortion degree on the patient information display screen before the start of ultrasound transmission / reception control The information is stored in the memory 102 while being associated with the information to be performed.

  Next, comparison processing by the development comparison unit 112 will be described. FIG. 15 is a flowchart showing the comparison process of the development comparison unit 112.

  First, the development comparison unit 112 divides the degree of distortion into each category, and counts the number of sample points belonging to the category (step S11).

  In the memory 102, a predetermined degree of distortion is stored in advance as a threshold value. This threshold value has a value indicating the boundary of the section. In step S <b> 11, the development comparison unit 112 reads this threshold value and compares each degree of distortion stored in the memory 102 with the threshold value. As a result of the comparison, if the value is equal to or greater than the threshold value, the number of sample points for the category equal to or greater than the threshold value is counted up by one. If the result of the comparison is less than the threshold value, the number of sample points for the section less than the threshold value is counted up by one.

  Next, the development comparison unit 112 calculates the ratio of each sample point belonging to each section in the degree of distortion (step S12).

  In this step S12, the development comparison unit 112 totals the number of sample points for the division above the threshold and the number of sample points for the division below the threshold. And the ratio with respect to the sum total of the sample score with respect to the division | segmentation more than a threshold is calculated, and the ratio with respect to the sum total of the sample score with respect to the division | segmentation less than a threshold value is calculated.

  Then, the development comparison unit 112 ends the creation of the development frequency by associating the subject attribute information with the ratio of each sample point belonging to each section (step S13).

  In this step S13, the development comparison unit 112 compares the nationality, gender, age, and the ratio stored in the memory 102 into the ratio of the total number of sample points for the division above the threshold and the proportion of the total number of sample points for the division below the threshold. Further, the development frequency is created by associating the information for identifying the subject and stored in the memory 102.

  When the development degree is created from the measured distortion degree, the development comparison unit 112 creates an image in which the comparison target and the development degree prepared in advance are arranged and displayed on the monitor 9 (step S14).

  The development frequency to be compared is stored in advance in the memory 102 in the form of an electronic dictionary as shown in FIG. FIG. 16 is a data structure diagram showing the development frequencies to be compared that are stored in advance. The development frequency to be compared is the same kind of data as the measured development frequency, and is the development frequency measured in the past of the same subject or the development frequency of a famous person such as an athlete.

  Similar to the measured developmental frequency, the comparison target developmental frequency is the total of the patient's name that identifies the subject and the number of sample points that have a threshold or higher, for example, the degree of distortion is X mm / sec or higher. It consists of a numerical value indicating the ratio to the number of sample points and a numerical value indicating the ratio of the number of sample points whose degree of distortion is less than X mm / sec to the total number of sample points.

  In step S14, the development comparison unit 112 causes the monitor 9 to display a screen for selecting a comparison target in advance. On this screen, for example, the subject attribute information is acquired and displayed from the development frequency of the comparison target converted into an electronic dictionary. When one comparison target is selected using the console 120 based on this screen, the development level associated with the same nationality, gender, age, or information identifying the subject as the selected comparison target The dictionary is read from the memory 102, and an image arranged with the measured development degree is created and displayed. In this comparison target selection process, for example, when creating a comparison table with developmental degrees measured in the past for the same subject, the same information as the information for identifying the subject for which an ultrasonic image is taken is associated. The obtained development frequency is read from the memory 102.

  Next, a future muscle growth prediction process by the growth prediction processing unit 113 will be described. FIG. 17 is a flowchart showing the development prediction processing by the development prediction processing unit 113.

  First, the development prediction processing unit 113 calculates a predicted increase / decrease rate after a predetermined number of years from the age of the subject from a general average distortion degree for each age prepared in advance (step S21).

  FIG. 17 is a diagram showing a general average degree of distortion for each age prepared in advance. As shown in FIG. 17, the memory 102 stores in advance a general distortion degree average for each nationality, gender, and age. The average distortion degree is an average of distortion degrees acquired from each sample point. The development prediction processing unit 113 calculates the average skewness average associated with the age of the subject and the age after a predetermined number of years from the average skewness average associated with the nationality and sex of the subject. Each is selected from the memory 102. Then, the general average skewness value associated with the age of the subject is divided by the general skewness average associated with the age after a predetermined number of years. The predetermined number of years is, for example, one year later. In addition, it may be after the number of years corresponding to the numerical value input on the console 120.

  When the predicted increase / decrease rate is calculated, the development prediction processing unit 113 calculates the average distortion degree of the subject (step S22), and obtains a predicted value of the average distortion degree by multiplying the average distortion degree of the subject by the predicted increase / decrease rate. (Step S23). The average distortion degree of the subject is calculated by calculating the average distortion degree of each measured sample point.

  When calculating the predicted value of the average degree of distortion, the development prediction processing unit 113 creates a screen on which the predicted value is arranged and displays it on the monitor 9 (step S24).

  As described above, since the ultrasonic diagnostic apparatus according to the present embodiment has a mechanism for exercising muscles that are related to consciousness by low frequency, stable including the case where the muscles are not consciously moved due to pathology or the like. It is possible to visualize the exercise of the muscles. In addition, since this stable muscle motion can be visualized, the degree of distortion of the comparison target muscle that is not affected by the environment or physical condition can be sampled, and high-precision comparison and development prediction are possible.

  Further, by selectively applying a pulse signal to the plurality of arranged positive electrodes 14 and negative electrodes 15, a low-frequency current can be transmitted with various directivities and various widths. Therefore, by referring to the ultrasonic image, it is possible to give a desired electrical stimulation in units of fibers regardless of the direction in which the muscle fibers extend or have any width.

  In this embodiment, the low-frequency current has been described on the assumption of a direct current. However, an alternating current may be used, and in the case of an alternating current, any electrode can be the positive electrode 14 and the negative electrode 15.

It is a schematic diagram which shows the external appearance of the ultrasonic probe with a low frequency transmission mechanism which concerns on a 1st example, (a) is a side view, (b) is the front view seen from the head side. It is a schematic diagram which shows the external appearance of the ultrasonic probe with a low frequency transmission mechanism which concerns on a 2nd specific example. It is a schematic diagram which shows the internal structure of the ultrasonic probe with a low frequency transmission mechanism which concerns on a 2nd specific example. It is a figure which shows the structure which switches the positive electrode and negative electrode which apply a pulse. It is a schematic diagram which shows the example of mounting | wearing of the ultrasonic probe with a low frequency transmission mechanism which concerns on a 1st specific example. It is a schematic diagram which shows the example of mounting | wearing of the ultrasonic probe with a low frequency transmission mechanism which concerns on a 2nd specific example. It is a block diagram which shows the structure of an ultrasonic diagnosing device main body. It is a block diagram which shows the further detailed structure of a controller. It is a schematic diagram which shows the screen which assists operation which inputs the direction and range in case the ultrasonic probe with a low frequency transmission mechanism which concerns on a 1st specific example is connected to the ultrasonic diagnostic apparatus main body. It is a schematic diagram which shows the screen which assists operation which inputs the direction and the range in case the ultrasonic probe with a low frequency transmission mechanism which concerns on a 2nd example is connected to the ultrasonic diagnostic apparatus main body. It is a schematic diagram which shows the 1st specific example which applies a pulse signal to the positive electrode and negative electrode which are arrange | positioned at the ultrasonic probe with a low frequency transmission mechanism which concerns on a 2nd specific example. It is a schematic diagram which shows the 2nd specific example which applies a pulse signal to the positive electrode and negative electrode which are arrange | positioned at the ultrasonic probe with a low frequency transmission mechanism which concerns on a 2nd specific example. It is a schematic diagram which shows the 3rd specific example which applies a pulse signal to the positive electrode and negative electrode which are arrange | positioned at the ultrasonic probe with a low frequency transmission mechanism which concerns on a 2nd specific example. It is a flowchart which shows the measurement process of a distortion degree. It is a flowchart which shows a comparison process. It is a data structure figure which shows the development frequency used as a comparison object. It is a flowchart which shows a development prediction process. It is a figure which shows the general distortion degree average for every age prepared beforehand.

Explanation of symbols

1, 1a, 1b Ultrasonic probe with low frequency transmission mechanism 11 Head 12 Adhesion pad 13 Puncture needle 14 Positive electrode 15 Negative electrode 16 Lead wire 17 Code 18 Switch 2 Ultrasonic diagnostic apparatus main body 3 Low frequency pulse signal transmission unit 4 Pulse signal transmitter for ultrasonic wave 41 Pulse generator 42 Delay circuit 43 High power circuit 5 Receiver 61 B / M processor 62 CFM processor 7 DSC
8 Video I / F
9 Monitor 91 First image 92 Second image 93 Electrode mark 94 Low frequency transmission direction mark 95 Cursor 96 Puncture needle mark 100 Controller 101 CPU
102 Memory 110 Low Frequency Current Control Unit 111 Strain Measurement Unit 112 Development Comparison Unit 113 Development Prediction Processing Unit 120 Console

Claims (8)

An ultrasonic probe having an ultrasonic wave transmitting / receiving surface in the head;
A positive electrode and a negative electrode that are arranged on the ultrasonic probe with the head interposed therebetween, and are applied with a low frequency pulse to apply electrical stimulation to the living body;
Image processing means for generating an image of the living body based on a reflected wave received from the electrically stimulated living body by the ultrasonic probe;
Display means for displaying the image;
Strain measurement means for measuring a value indicating strain of the living body due to the electrical stimulation based on the image;
It is arranged along the edge of the head, and has an attaching part attached to the living body,
The positive electrode and the negative electrode are scattered and arranged on the surface of the sticking part to be stuck to the living body,
An ultrasonic diagnostic apparatus characterized by the above. An ultrasonic probe having an ultrasonic wave transmitting / receiving surface in the head;
A positive electrode and a negative electrode that are arranged on the ultrasonic probe with the head interposed therebetween, and are applied with a low frequency pulse to apply electrical stimulation to the living body;
Image processing means for generating an image of the living body based on a reflected wave received from the electrically stimulated living body by the ultrasonic probe;
Display means for displaying the image;
Strain measurement means for measuring a value indicating strain of the living body due to the electrical stimulation based on the image;
A pair of puncture needles arranged on the ultrasonic probe across the head,
The positive electrode and the negative electrode are accommodated in the puncture needle;
Ultrasonic diagnostic apparatus said. An ultrasonic probe having an ultrasonic wave transmitting / receiving surface in the head;
A positive electrode and a negative electrode that are arranged on the ultrasonic probe with the head interposed therebetween, and are applied with a low frequency pulse to apply electrical stimulation to the living body;
Image processing means for generating an image of the living body based on a reflected wave received from the electrically stimulated living body by the ultrasonic probe;
Display means for displaying the image;
Strain measurement means for measuring a value indicating strain of the living body due to the electrical stimulation based on the image;
The positive electrode and the negative electrode are arranged in a row with the counter electrodes facing each other,
Each positive switch corresponding to each of the plurality of positive electrodes,
Each negative side switch corresponding to each of the plurality of negative electrodes,
Low frequency current control means for selectively switching on or off the positive side switch and the negative side switch independently;
Ultrasonic diagnostic apparatus comprising the. The low frequency current control means includes
By turning on the positive side switch and the negative side switch corresponding to the positive electrode and the negative electrode that are not opposed to each other, a low-frequency current directed obliquely with respect to the arrangement direction of the positive electrode and the negative electrode is generated. Sending,
The ultrasonic diagnostic apparatus according to claim 3 . The low frequency current control means includes
By turning on the positive electrode side switch and the negative electrode side switch corresponding to a plurality of adjacent positive electrodes and negative electrodes, a low frequency current is transmitted to a predetermined width of the living body,
The ultrasonic diagnostic apparatus according to claim 3 . The display means displays the positive electrode and the negative electrode to which a pulse is applied in an individually selectable manner,
The low frequency current control means turns on the positive side switch and the negative side switch corresponding to the positive electrode and the negative electrode selected based on the display,
The ultrasonic diagnostic apparatus according to claim 3 . A development frequency for evaluating the development of the living body based on the value indicating the distortion is stored in advance as a comparison target, and the development frequency based on the value indicating the measured distortion is stored in advance as the comparison target. A development comparison unit for simultaneously displaying the development frequency on the display means;
Further comprising
The ultrasonic diagnostic apparatus according to claim 1. A general value indicating the distortion for each age is stored in advance, and based on the predicted increase / decrease rate of the distortion after a predetermined number of years from the age of the subject based on the general value, and the value indicating the measured distortion, Further comprising a development prediction means for calculating a predicted value of strain of the living body after the predetermined number of years;
The ultrasonic diagnostic apparatus according to claim 1.