JP2008229245A - Ultrasonic diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To solve the problem that the conventional ultrasonic diagnostic apparatus needs a complicated electronic circuit to clean ultrasonic beams electronically and causes a large apparatus and a high cost. <P>SOLUTION: The ultrasonic diagnostic apparatus has an ultrasonic probe, and gives a drive signal to the ultrasonic probe to transmit the ultrasound and simultaneously takes an echo signal from the ultrasonic probe, and forms the diagnostic information from the echo signal, and the ultrasonic probe has an ultrasonic transducer buried in a sonic transmitter, and it has an angular velocity sensor for detecting the inclined angle of the ultrasonic transducer, at least two acceleration sensors for detecting the acceleration in the perpendicular direction to the axis of the ultrasonic transducer and the ultrasonic probe, at least an acceleration sensor for detecting the acceleration in the axial direction of the ultrasonic transducer and the ultrasonic probe, and a base plate equipped with the ultrasonic transducer, the angular velocity sensor, and the acceleration sensor, and it is characterized in that the scanning of the ultrasonic probe is performed manually. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and more particularly, to a small apparatus that generates diagnostic information based on ultrasonic waves and can be easily used while improving measurement accuracy.

  The ultrasound diagnostic device scans the inside of the diagnostic object with an ultrasound beam, receives an ultrasound echo signal, obtains image data corresponding to the intensity of the ultrasound echo signal, and thereby a so-called two-dimensional image called a B-mode image A cross-sectional image is generated. An ultrasonic diagnostic apparatus is generally used in hospitals and the like and is widely known, but is not assumed to be used by general consumers in arbitrary places and situations. However, with the widespread use of information terminal equipment, it is becoming common for consumers to carry advanced information equipment personally and use it in any location or situation, so it has been used in medical institutions in the past. Even if it is an ultrasonic diagnostic device, if the consumer can carry it personally and use it in any place or situation, the convenience will be significantly improved and it will contribute significantly to personal health management. .

  There is also an apparatus for measuring the thickness of subcutaneous fat using an ultrasonic signal for this purpose (see Patent Document 1). In the apparatus shown in FIG. 7, the ultrasonic drive detection circuit is made compact, and the ultrasonic signal processing is performed by a personal computer equipped with an interface, so that the entire system is made compact and usable at home.

JP 2005-152605 A (page 3)

  In the prior art disclosed in Patent Document 1, even though it is portable, ultrasonic waves are transmitted by gradually shifting the phase from ultrasonic transducers arranged in a plurality of arrays in order to acquire a two-dimensional in-vivo cross-sectional image. The ultrasonic wave front is controlled to sweep and focus the ultrasonic beam.

  In such a configuration, it is obvious that a very complicated electronic circuit is required as in the case of a stationary ultrasonic diagnostic apparatus, resulting in a high price. Moreover, even though it is portable, there is a limit, and there is a problem that it is not as small and light as a stethoscope, for example, so that a doctor can always carry it around and use it immediately.

  In order to solve the above-described problems caused by the conventional technology, the present invention provides a low-cost ultrasonic diagnosis that can be easily carried by a non-invasive and simple measurement of the internal state of a living body with a simple configuration ultrasonic diagnostic apparatus. An object is to provide an apparatus.

  In order to achieve the above object, the ultrasonic diagnostic apparatus of the present invention employs the following configuration.

Have an ultrasonic probe,
Applying a drive signal to the ultrasonic probe to transmit the ultrasonic wave and capturing an echo signal from the ultrasonic probe,
An ultrasonic diagnostic apparatus that generates diagnostic information based on an echo signal,
The ultrasonic probe has an ultrasonic transducer embedded in the sound transmission body,
An angular velocity sensor for detecting the tilt angle of the ultrasonic transducer;
A plurality of acceleration sensors for detecting acceleration in a direction perpendicular to the axis of the ultrasonic probe;
An acceleration sensor that detects the axial acceleration of the ultrasonic probe;
It has the board | substrate which comprises an ultrasonic transducer, an angular velocity sensor, and an acceleration sensor.

The ultrasonic diagnostic apparatus of the present invention is
A signal drive detection unit,
The signal drive detection unit preferably has a portion for storing the ultrasonic probe and a detection sensor for detecting the presence or absence of the ultrasonic probe.

  According to the present invention, anyone can easily and accurately measure an in-vivo two-dimensional cross-sectional image using ultrasound, and can be realized at an extremely low price, such as measuring the thickness of subcutaneous fat and malignant tumors. This has the effect that detection can be easily performed by an individual. Since an angular velocity sensor and an acceleration sensor for detecting the movement of the ultrasonic sensor are provided, it is possible for the measurer to control the operation of the entire apparatus by giving an appropriate movement to the ultrasonic probe. Thereby, the operability is remarkably improved and the number of mechanical switches can be reduced, which contributes to the reduction of failure.

  Exemplary embodiments of an ultrasonic diagnostic apparatus according to the present invention will be described below in detail with reference to the accompanying drawings, and some terms will be described in advance. First, the axis of the ultrasonic probe is a central axis of the ultrasonic probe 3 configured in a cylindrical shape, and is shown as an axis 400 in FIG. The angular velocity sensor detects a rotational angular velocity. In the present invention, the angular velocity sensor is a vibration gyro sensor using a crystal. Also, the main object of the present invention is to easily obtain an in-vivo B-mode image without manually adopting a complicated electronic circuit configuration by manually rotating an ultrasonic probe and detecting the rotation amount with an angular velocity sensor. . By the way, when the ultrasonic probe is rotated manually, the rotation center of the ultrasonic probe moves spatially depending on the shake of the hand being operated or the state of the living tissue of the measured object. It is necessary to detect the rotation center at.

  In addition, the motion of the ultrasonic probe can be divided into a rotational motion centered on the rotational center in a coordinate system fixed to the ultrasonic probe and a translational motion of the rotational center. The rotation center in the coordinate system fixed to the ultrasonic probe of this ultrasonic probe will be referred to as a local rotation center. Further, the coordinates indicating the position of the reference point of the ultrasonic probe in the absolute space are referred to as position coordinates. The reference point of the ultrasonic probe is the tip of the ultrasonic probe. It should be mentioned in advance that the detection of the rotation center of the ultrasonic probe in the absolute space is performed by three acceleration sensors provided in the ultrasonic probe.

  FIG. 4 shows an overall block diagram of the ultrasonic diagnostic apparatus of the present invention. This ultrasonic diagnostic apparatus detects the acceleration in the axial direction of the ultrasonic probe, the vibration gyro sensor 2, the two acceleration sensors 4a and 4b that detect acceleration in the direction perpendicular to the ultrasonic probe axis, and the ultrasonic probe. An ultrasonic probe 3 on which one acceleration sensor 4d is mounted, a transmission unit 4 that generates a drive signal for generating ultrasonic waves, and a reception unit that receives electrical signals from the ultrasonic transducer 1 and the vibration gyro sensor 2 5 and a signal processing unit 8 that performs signal processing for displaying internal biological information as a B-mode image on the monitor from the ultrasonic echo signal and angle information. Further, the ultrasonic diagnostic apparatus includes an input unit 7 and a display unit 9.

The ultrasonic probe 3 is for transmitting and receiving ultrasonic waves by bringing its front surface into contact with the surface of the subject, and is provided with the ultrasonic transducer 1 at the tip portion thereof. The ultrasonic transducer 1 is an electroacoustic transducer, and has a function of converting an electric pulse into an ultrasonic pulse at the time of transmission and converting an ultrasonic signal into an electric signal at the time of reception. The ultrasonic frequency that greatly affects the resolution and sensitivity of the ultrasonic echo image is substantially determined by the thickness of the piezoelectric body 101 of the ultrasonic transducer 1 and the material and thickness of the backing material 120 shown in FIG. The ultrasonic probe 3 is configured to be small and light, and is connected to a transmitter 4 and a receiver 5 described later by a coaxial cable.

  The vibration gyro sensor 2 utilizes the property that when a piezoelectric element is vibrated and a rotational angular velocity Ω is applied to the piezoelectric element, a Coriolis force is generated in a direction perpendicular to the original vibration. This Coriolis force is extracted as an output voltage by the detecting piezoelectric element. Since the vibration gyro sensor 2 detects the rotational angular velocity, the detection signal is digitized by the AD converter 57, integrated by the integration calculator 82, converted into an azimuth angle, and stored as azimuth angle information of the ultrasonic transducer 1. 86.

  The acceleration sensors 4a, 4b, and 4d extract the electromotive force of the piezoelectric body generated by the acceleration when the acceleration is applied in a direction perpendicular to the axis 400 of the ultrasonic probe and a direction parallel to the axis 400. From the acceleration information obtained by this acceleration sensor, the coordinates of the rotation center of the ultrasonic probe when the ultrasonic probe is manually rotated are obtained. The detected acceleration signal is amplified and calculated by the rotation center detection circuit 58 and the position coordinate detection circuit 60 with high input impedance, and then digitized by the AD converters 59 and 61, and the RAM 88 as rotation center coordinate information of the ultrasonic probe. , 89.

The transmission unit 4 includes a pulse generator 43, a pulse delay circuit array 42, and an FET switch array 41. The pulse generator 43 generates a reference pulse of the ultrasonic pulse radiated into the subject. The pulse delay circuit array 42 is composed of a plurality of independent delay circuits equal in number to the ultrasonic transducers 1 used for transmission, determines the convergence distance of the ultrasonic beam at the time of transmission, and sets the ultrasonic wave to a predetermined depth. Is a delay circuit for giving a delay time for converging, and drives a plurality of ultrasonic transducers at different timings. The FET switch array 41 is an FET switch circuit array that generates a high-voltage pulse for driving the ultrasonic transducer 1. The FET switch array 41 has the same number of independent drive circuits as the ultrasonic transducers 1 used for transmission in the same manner as the pulse delay circuit array 42, and the ultrasonic transducers built in the ultrasonic probe 3. 1 is driven to form a driving pulse for emitting ultrasonic waves.

  The receiving unit 5 includes a signal gate 51, a preamplifier 52, a logarithmic conversion amplifier 53, and an AD converter 54. The preamplifier 52 amplifies a minute signal converted into an electric signal by the ultrasonic transducer 1 to ensure sufficient S / N. In general, the received signal from within the subject has an amplitude with a wide dynamic range of 80 dB or more, so that the weak signal is emphasized and the dynamic range is narrowed so that it can be displayed as an image. The amplifier 53 detects the input signal, removes the ultrasonic frequency component, detects only the amplitude of the envelope, and simultaneously logarithmically converts the amplitude. The AD converter 54 AD converts the output signal of the logarithmic conversion amplifier 53. The transmission unit 4 and the reception unit 5 constitute a signal drive detection unit 300 shown in FIG. The signal drive detection unit 300 is provided with an ultrasonic probe detection sensor 310 serving as a detection sensor.

The input unit 7 is used for inputting operation conditions of the apparatus from the operation panel. It is also possible to instruct various image quality condition settings. The signal processing unit 8 performs arithmetic processing from the received ultrasonic signal, the signals from the vibration gyro sensor 2 and the acceleration sensors 4a, 4b, and 4d,
B-mode image data is calculated. The display unit 9 is composed of a color monitor and can display B-mode image data.

  The CPU 81 temporarily stores the signals from the receiving unit 5 in the RAMs 86, 87, 88, and 89, performs coordinate conversion 85 according to a predetermined calculation algorithm, and displays the converted data on the display unit 9 as a B-mode image. The CPU 81 has a storage means such as a ROM for storing programs and the like therein, and a RAM for storing data, intermediate processing results, and the like, and generally performs arithmetic processing in accordance with instructions of the programs stored in the ROM. A microprocessor.

  Next, the structure of the ultrasonic probe 3 in the first embodiment of the ultrasonic diagnostic apparatus of the present invention will be described with reference to FIG. The ultrasonic probe 3 includes a cylindrical casing 38, a substrate 31, an ultrasonic transducer 1, a vibration gyro sensor 2, two acceleration sensors 4 a and 4 b and one acceleration sensor 4 d, a sound transmission body 32, a connector 34, and a coating 39. ing. The substrate 31 also has a role of a base for fixing the acoustic wave transmission body 32 and the arrangement of the connector 34, the ultrasonic transducer 1, the vibration gyro sensor 2, the acceleration sensors 4a, 4b, and 4c. The connector 34 connects to the receiving unit 5. Electrical signals from the ultrasonic transducer 1, the vibration gyro sensor 2, and the acceleration sensors 4a, 4b, and 4d are connected to the connector 34 via a wiring connection unit on the substrate 31 (not shown).

  In the ultrasonic diagnostic apparatus of the present invention, the ultrasonic probe 3 is pressed against the living body, and is manually rotated and scanned around the contact portion between the ultrasonic probe 3 and the living body so that the ultrasonic beam is swept through the target living tissue. By doing so, the ultrasonic echo signal from the living body, the azimuth angle of the ultrasonic probe 3 detected by the vibration gyro sensor 2, the acceleration information detected from the two acceleration sensors 4a and 4b, and the axis detected from one acceleration sensor 4d A B-mode image of the internal tissue of the living body is constructed by applying coordinate transformation 85 from the amount of directional movement.

  The ultrasonic waves reflected from the interface between tissues having different acoustic impedances inside the living body are received by the same ultrasonic transducer 1 as that used for transmission, and the ultrasonic transducer 1 generates an echo signal as a received signal. This echo signal is separated from the transmission signal by the signal gate 51, and only the echo signal is stored in the RAM 87 via the preamplifier 52, logarithmic conversion amplifier 53, and AD converter 54.

A detailed description of the ultrasonic probe 3 will be described below. The ultrasonic transducer 1 of the present invention comprises a plurality of concentrically arranged piezoelectric elements configured to be used for both transmission and reception.
When the drive pulse transmitted from the transmission unit 4 is applied to the ultrasonic transducer 1, the piezoelectric element in the ultrasonic transducer 1 is excited by the drive pulse to generate an ultrasonic wave.

  The higher the natural resonance frequency of the ultrasonic transducer 1 is, the higher the resolution is. In the present invention, description will be made on the assumption of tissue diagnosis inside the living body, so that the natural resonance frequency is 4 MHz.

  Therefore, in the ultrasonic echo method used in the present invention, first, an electric pulse having a pulse width of about 200 ns is generated at a reference frequency of 10 kHz, that is, at a time interval of 100 μs by the pulse generator 43 of the ultrasonic transmission unit 4, and this electric pulse is generated. Delayed so as to realize so-called dynamic focus in which the focal position changes with time so that the ultrasonic wavefront generated by the ultrasonic transducer 1 is successively converged at predetermined points in the depth direction. give.

  In the present invention, the focusing method in the beam traveling direction of the ultrasonic wave radiated from the ultrasonic transducer 1 is the dynamic focus, and only the scanning of the ultrasonic beam is manually performed. This remarkably simplifies the configuration of the electronic circuit and reduces the size of the device. Furthermore, the ultrasonic wave emitted from the ultrasonic transducer 1 may be emitted from an ultrasonic transducer having a fixed curvature, propagated as a spherical wave, and converged at a predetermined position without using dynamic focus. In this case, the apparatus can be further reduced in size and price. However, in this case, the focal depth of the ultrasonic beam is not deep, and the sharpness of the obtained image is somewhat inferior to that of the dynamic focus, but it is sufficient for practical use.

  As shown in FIG. 1, the ultrasonic transducer 1 of the ultrasonic diagnostic apparatus of the present invention is provided inside a sound wave transmitting body 32. The acoustic wave transmission body 32 is preferably composed of a polymer gel such as silicon gel having an acoustic impedance comparable to that of the skin. The acoustic wave transmission body 32 is covered and protected by a film 39 such as polyurethane or polystyrene. If the sonic transmission body 32 is made to be replaceable by a cap type, the coating 39 need not be used.

  The structure of the ultrasonic transducer 1 will be described with reference to FIG. As the piezoelectric body 101 used for the ultrasonic transducer 1, for example, a polymer piezoelectric material such as PVDF (polyvinylidene fluoride), or an inorganic piezoelectric material such as these polymer piezoelectric materials and lead zirconate titanate (PZT). Or a complex thereof. A front electrode 110 and a back electrode 111 are formed on both surfaces of the piezoelectric body 101. One end of a lead wire (not shown) is electrically connected to the electrode and the back electrode. In order to achieve a resonance frequency of 4 MHz with respect to an electric pulse width of 200 ns, the thickness of the piezoelectric body 101 is preferably 50 μm to 60 μm. Also, the ultrasonic wave toward the back surface is reflected to the front surface side by the backing material 120 made of a copper plate having a thickness of 40 μm, and an ultrasonic pulse with a short pulse width is efficiently generated. In order to make ultrasonic waves enter the living body as a thin beam, the diameter of the piezoelectric body 101 is preferably 4 to 5 mm. The front surface of the piezoelectric body is covered with a protective film (not shown).

  The backing material 120 is fixed to the base body 130. The base 130 is a fixed substrate for the backing material 120 and the piezoelectric body 101, and is fixed only around the backing material 120 so that the backing material 120 vibrates under suitable conditions. A high-viscosity polymer gel 140 is affixed to the opposite side of the backing material 120 to the PVDF to absorb and remove unnecessary vibration of the backing material.

  The piezoelectric body 101 generates ultrasonic waves in a pulsed manner by applying a pulse voltage of about 20 V between the lead wires. At this time, the energy incident on the living body is approximately 4 mW, and it may be considered that there is no influence on the living body.

  The vibration gyro sensor 2 will be described. The vibration gyro sensor 2 may be a general vibration gyro sensor, but a three-leg vibration gyro sensor is used in the present invention. The tripod vibration gyro sensor extracts a Coriolis force generated in a direction perpendicular to the original vibration as an output voltage by a detection piezoelectric body when a rotational angular velocity Ω is applied to the vibrating piezoelectric body. Since the vibration gyro sensor 2 detects the rotational angular velocity, the detection signal is digitized by the AD converter 57, and then the integration calculation 82 is performed and recorded in the RAM 86 as the azimuth angle reference information of the ultrasonic probe 1.

The acceleration sensors 4 a and 4 b are fixed so that the acceleration detection direction is perpendicular to the axis 400 of the ultrasonic probe 3 and parallel to the substrate 31. The acceleration sensor 4d is fixed so that the acceleration detection direction is parallel to the axis 400 of the ultrasonic probe. Since the acceleration sensor detects acceleration, the detection signal is amplified by the high-input-impedance axial acceleration detection circuit 60, digitized by the AD converter 61, and R as acceleration information in the direction of the axis 400 of the ultrasonic probe 3.
Recorded in AM84.

  Next, a method for manually rotating the ultrasonic probe 3 to obtain an in-vivo B-mode image will be described in detail with reference to FIGS. When the ultrasonic probe 3 (not shown) is manually rotated, as schematically shown in FIG. 2, generally, the hand operating the ultrasonic probe 3 or the living body surface 700 of the measurement object is measured. Depending on the state of the internal tissue 750 or the living body, the rotation center 420 of the ultrasonic probe 3 moves from 420a to 420f, for example, so that it is necessary to detect the rotation center of the ultrasonic probe 3. For detection of the rotation center, the local rotation center of the ultrasonic probe 3 and the position coordinates of the ultrasonic probe 3 are obtained. The position coordinates of the ultrasonic probe 3 are calculated from the amount of parallel movement of the ultrasonic probe 3 in the absolute space by obtaining the acceleration in the direction of the axis 400 of the ultrasonic probe 3 and considering the azimuth angle at that time.

  First, in order to obtain the instantaneous local rotation center of the ultrasonic probe 3, as shown in FIG. 3, the acceleration sensors 4a and 4b detect acceleration in a direction perpendicular to the axis 400 of the ultrasonic probe 3 at that position, The instantaneous local rotation center of the ultrasonic probe 3 is determined from the positive / negative and magnitude of the acceleration signal by the following procedure.

  In FIG. 3, the distance from the tip of the ultrasonic probe 3 indicating the position coordinates of the ultrasonic probe 3 of the acceleration sensor 4a is La, and the distance from the tip of the ultrasonic probe 3 of the acceleration sensor 4b is Lb. d = La−Lb. The distance from the tip of the ultrasonic probe 3 at the local rotation center of the ultrasonic probe 3 is Lc, the output of the acceleration sensor 4a is Va, and the output of the acceleration sensor 4b is Vb. Let the ratio of Va and Vb be κ. That is, κ = Va / Vb. This division can be performed using a general operational amplifier dedicated to division, for example, AD534, and the input can be Va and Vb, and κ can be obtained as the output.

When the rotation operation of the ultrasonic probe 3 is actually performed manually, the local rotation center of the ultrasonic probe 3 is not fixed at a specific position and is in various positions with different Lc. Depending on the positional relationship between the two acceleration sensors 4a and 4b, the following three cases can be considered. In each case, Lc is obtained as follows using d, κ, and Lb.
1) When the local rotation center of the ultrasonic probe 3 is closer to the living body than the acceleration sensor 4b,
Lc = d / (κ−1) −Lb
2) When the local rotation center of the ultrasonic probe is outside the acceleration sensor 4a (away from the living body),
Lc = −d / (κ−1) + Lb
3) When the local rotation center of the ultrasonic probe is between the acceleration sensor 4a and the acceleration sensor 4b,
Lc = d / (1-κ) + Lb
From the above formula, the distance Lc from the tip of the ultrasonic probe 3 at the local rotation center of the ultrasonic probe 3 is obtained.

  Next, a displacement in the direction of the axis 400 of the ultrasonic probe 3 is obtained by performing a numerical operation such as a general difference method from the output of the acceleration sensor 4d, and the position coordinates of the ultrasonic probe 3 are calculated.

  The rotation center coordinates in the absolute space of the ultrasonic probe 3 can be obtained from the local rotation center coordinates of the ultrasonic probe 3 and the position coordinates of the ultrasonic probe 3, and a B-mode image can be constructed.

  Since it is almost impossible to rotate the ultrasonic probe 3 at a completely constant angular velocity by manual scanning, the acceleration signal cannot be exactly zero. Therefore, the division of κ = Va / Vb does not make Vb 0 and the quotient does not become infinite. However, the output of the operational amplifier corresponding to κ may be a saturated output that depends on the power supply voltage. In this case, Vb is very small. Therefore, when the output of the operational amplifier is saturated, the ultrasonic probe 3 is performing a rotational motion around the position of the acceleration sensor 4b. It can be approximated.

Next, a method for constructing a B-mode image using the ultrasonic diagnostic apparatus of the present invention will be described.
For example, the ultrasonic probe 3 is first placed so as to be perpendicular to the living body surface at time t0. Here, the output of the integration calculation 82 is set to 0 V by electrical resetting by a switch (not shown) so that the azimuth angle of the ultrasonic probe 3 becomes 0 °. The rotational scanning operation is started and the ultrasonic probe 3 is rotated at an appropriate speed up to a predetermined negative angle. Let that time be t1. Then, the ultrasonic probe 3 is rotated to a positive predetermined angle, preferably at a constant angular velocity.

  During this time, the ultrasonic transducer 1 transmits an ultrasonic wave to the subject, receives an ultrasonic echo reflected from the interface of the tissue with different acoustic impedance inside the living body after a certain period of time, and the ultrasonic echo signal performs an appropriate process. After being applied, it is stored in the RAM 87. The detected angular velocity is integrated, and the azimuth angle of the ultrasonic probe 3 at the corresponding time is stored in the RAM 86 with reference to the normal to the living body surface.

  Simultaneously with the rotational scanning, the B-mode image in the living body is obtained by performing general coordinate conversion from the azimuth angle information of the ultrasonic probe 3, the local rotation center coordinate information, the position coordinate of the ultrasonic probe 3, and the ultrasonic echo signal information. Can be generated. The obtained B-mode image is displayed on the display unit 9. In addition, for the purpose of obtaining a fine B-mode image, the azimuth angle information, the local rotation center coordinate information of the ultrasonic probe 3 and the ultrasonic probe 3 stored in the RAM 86, 88, 89 and RAM 87 after the end of the rotational scanning. Advanced image processing can also be performed from the position coordinates and ultrasonic echo signal information.

  In the present invention, since the gyro sensor and the acceleration sensor for detecting the spatial movement of the ultrasonic probe 3 are provided, the measurement person gives an appropriate movement to the ultrasonic probe 3 so that the operation of the entire apparatus can be performed in software. It is possible to control. For example, the measurement is terminated when it is left at a final position for a predetermined time, for example, 2 seconds. Thereby, the operability is remarkably improved and the number of switches can be reduced, which contributes to the reduction of failure.

The method for constructing a B-mode image with the ultrasonic diagnostic apparatus of the present invention using what has been described above is a step of the actual procedure for operating the ultrasonic probe 3 housed in the signal drive detection unit 300 shown in FIG. I will explain later.

Step 1:
When the measurer takes out the ultrasonic probe 3 contained in the signal drive detection unit 300 from the signal drive detection unit 300, the ultrasonic probe detection sensor 310 serving as a detection sensor detects that the ultrasonic probe 3 has been taken out. The power source of the signal drive detection unit 300 and the power source of the signal processing unit 8 and the display unit 9 are restored from the sleep state and turned on.

Step 2:
The measurer lightly presses the tip of the ultrasound probe 3 against the living body 700 and holds the ultrasound probe so that the central axis of the ultrasound probe is substantially perpendicular to the living body 700. This time is T1. In this state, the ultrasonic probe 3 is kept stationary for a predetermined time, for example, for about 2 seconds.

Step 3:
The CPU 81 monitoring the output of the vibration gyro sensor 2 determines that the value has become equal to or less than a predetermined value by stopping the ultrasonic probe 3, and the direction of the central axis of the ultrasonic probe 3 at that time is determined by the living body. A line corresponding to the vertical direction of the living body of the B-mode image to be displayed on the display unit 9 is determined with the vertical direction. Here, the azimuth angle of the ultrasonic probe 3 is electrically reset by a switch (not shown) so that the azimuth angle of the ultrasonic probe 3 becomes 0 ° so that the output of the integral calculation 82 becomes 0V.

Step 4:
A measurer manually rotates the ultrasonic probe 3 to an initial position for starting scanning at an appropriate speed. Normally, this time is T2, for example, -50 ° up to a predetermined negative angle. Therefore, the ultrasonic probe 3 is stopped again for a predetermined time, for example, about 2 seconds. The CPU determines that position as a measurement start.

Step 5:
The measurer manually rotates the ultrasonic probe 3 in the positive direction at a constant angular velocity. At this time, the angular velocity detected as the output of the vibration gyro sensor 2 is integrated by the integration operation 82 and determined as the azimuth angle of the ultrasonic probe 3 at the corresponding time. At the same time, the azimuth angle is stored in the RAM 86.

Step 6:
The CPU 81 arranges the B-mode time axis on the display unit 9 corresponding to the determined direction of the ultrasonic probe, calculates the local rotation center coordinates of the ultrasonic probe 3 from the outputs of the two acceleration sensors 4a and 4b, The rotation center coordinates are obtained from the position of the local rotation center and the position of the ultrasonic probe 3 in the absolute space, and the B-mode time axis is rotated for a minute time Δt around that position, thereby echoing the ultrasonic echo data. The luminance of the B-mode time axis is modulated corresponding to the corresponding time and displayed on the display unit 9 as a B-mode image.

Step 7:
The CPU 81 integrates the output of the acceleration sensor 4d corresponding to the elapsed minute time Δt, obtains the axial displacement of the ultrasonic probe 3 during the minute time Δt, and determines the position coordinates of the ultrasonic probe 3 as the ultrasonic probe 3. The position coordinates of the ultrasonic probe 3 are determined by shifting the displacement in the direction of the central axis of the ultrasonic probe 3.

Step 8: The measurer rotates the ultrasonic probe 3 to the final position while repeating Step 4 to Step 7.

Step 9:
The measurer rotates the ultrasonic probe 3 to the final position, and then rests again for a predetermined time, for example, about 2 seconds. The CPU 81 that monitors the output of the vibration gyro sensor 2 determines that the value has become a predetermined value or less by stopping the ultrasonic probe 3, and determines that the measurement is completed.

Step 10:
When the measurer puts the ultrasonic probe 3 in the signal drive detection unit 300, the ultrasonic probe detection sensor 310 detects that the ultrasonic probe 3 has been put in, and the power source, the signal processing unit 8 and the display of the signal drive detection unit 300 are detected. The power supply of the unit 9 is set to the sleep state.

  In order to obtain a high-definition B-mode image, the azimuth angle information, ultrasonic echo signal information, and rotation center of the ultrasonic probe 3 stored in the RAM 86, RAM 87, RAM 88, and RAM 89 after the scanning of the ultrasonic probe 3 is completed. It is also possible to perform advanced image processing from the information and the position coordinates of the ultrasonic probe 3. The obtained B-mode image is displayed on the display unit 9.

  In step 3, the rotational angular velocity when the ultrasonic probe is rotated to a predetermined negative angle and brought to the initial scanning position is, for example, about 50 (degrees / second), and the time from T1 to T2 is 2 It should be around seconds. That is, the sweep angle is about 100 degrees. In step 4, since the angular velocity is detected by the vibration gyro sensor 2, the rotational speed does not necessarily have to be a constant angular velocity, and in principle, it may be arbitrary, but if it is extremely fast, the vibration gyro The electronic circuit that processes the signal of the sensor 2 may saturate the signal of the vibration gyro sensor 2 due to power supply voltage restrictions.

  As described above, according to the ultrasonic diagnostic apparatus of the present invention, anyone can easily and accurately measure a two-dimensional cross section in a living body as an ultrasonic B-mode image. Since the gyro sensor and the acceleration sensor for detecting the movement of the ultrasonic sensor are provided, it is possible for the measurer to control the operation of the entire apparatus by giving an appropriate movement to the ultrasonic probe. Thereby, the operability is remarkably improved and the number of switches can be reduced, which contributes to the reduction of failure. The ultrasonic diagnostic apparatus of the present invention can be applied to simple measurement such as subcutaneous fat thickness measurement, vein position measurement, detection of subdural hematoma or malignant tumor in the skull.

  Since the ultrasonic diagnostic apparatus of the present invention can easily measure a correct in-vivo cross-sectional image, it can be used not only in a hospital but also in a nursing facility. Since measurement at the bedside is easy, it is suitable for use in a subject who cannot place a load on the living body. Since the entire ultrasound diagnostic apparatus can be made small and light, it is also suitable for general household health management.

It is a figure explaining the ultrasonic probe part in embodiment of the ultrasonic diagnosing device of this invention. It is a figure of the scanning of the ultrasonic probe part in embodiment of the ultrasonic diagnostic apparatus of this invention. It is explanatory drawing of the method of calculating | requiring the rotation center of an ultrasonic probe part. 1 is a block diagram of an ultrasonic diagnostic apparatus of the present invention. It is a figure explaining the ultrasonic transducer of the ultrasonic diagnostic apparatus of this invention. It is a figure which shows the state which set the ultrasonic probe to the signal drive detection unit. It is a figure explaining the conventional ultrasonic diagnostic apparatus.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Ultrasonic transducer 2 Vibration gyro sensor 3 Ultrasonic probe 4a, 4b, 4d Acceleration sensor 32 Sonic wave transmission body 400 Axis

Claims (2)

Have an ultrasonic probe,
A drive signal is given to the ultrasonic probe to transmit an ultrasonic wave, and an echo signal is captured from the ultrasonic probe,
An ultrasonic diagnostic apparatus that generates diagnostic information based on the echo signal,
The ultrasonic probe has an ultrasonic transducer embedded in a sound transmission body,
An angular velocity sensor for detecting an inclination angle of the ultrasonic transducer;
A plurality of acceleration sensors for detecting acceleration in a direction perpendicular to the axis of the ultrasonic probe;
An acceleration sensor for detecting an axial acceleration of the ultrasonic probe;
An ultrasonic diagnostic apparatus comprising: a substrate including the ultrasonic transducer, the angular velocity sensor, and the acceleration sensor. A signal drive detection unit,
The ultrasonic diagnostic apparatus according to claim 1, wherein the signal-driven detection unit includes a portion that stores the ultrasonic probe and a detection sensor that detects the presence or absence of the ultrasonic probe.

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