WO2007003069A1 - Dispositif à ultrasons de diagnostic médical - Google Patents

Dispositif à ultrasons de diagnostic médical Download PDF

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Publication number
WO2007003069A1
WO2007003069A1 PCT/CN2005/000966 CN2005000966W WO2007003069A1 WO 2007003069 A1 WO2007003069 A1 WO 2007003069A1 CN 2005000966 W CN2005000966 W CN 2005000966W WO 2007003069 A1 WO2007003069 A1 WO 2007003069A1
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WO
WIPO (PCT)
Prior art keywords
data
signal
transmitter
computer
receiver
Prior art date
Application number
PCT/CN2005/000966
Other languages
English (en)
Chinese (zh)
Inventor
Pychnyi Mikhail
Papine Igor
Songgen Zhang
Guanzhong Ye
Qiang Zhou
Original Assignee
Teknova Medical Systems Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Teknova Medical Systems Limited filed Critical Teknova Medical Systems Limited
Priority to PCT/CN2005/000966 priority Critical patent/WO2007003069A1/fr
Publication of WO2007003069A1 publication Critical patent/WO2007003069A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8977—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using special techniques for image reconstruction, e.g. FFT, geometrical transformations, spatial deconvolution, time deconvolution
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52079—Constructional features
    • G01S7/5208—Constructional features with integration of processing functions inside probe or scanhead

Definitions

  • the present invention relates to a diagnostic apparatus, and more particularly to a medical ultrasonic diagnostic apparatus having a standard bus interface, which can be easily connected to a computer, and which can flexibly set parameters and change the number of probes. Background technique
  • Acoustic imaging in ultrasound diagnostic equipment is based on the use of focused ultrasound pulses to detect areas of the human body that are being studied.
  • a dedicated ultrasonic probe is required which can simultaneously focus the transmitted and received ultrasonic signals.
  • the area of the human body being studied is scanned in the focus area of the probe.
  • the ultrasonic beams are located in the same plane, either forming a set of parallel straight lines or forming a fan plane.
  • the reflected ultrasonic echo signals are recorded.
  • the distance to the reflection point, C is the propagation velocity of the sound wave in the soft tissue of the human body (about l Om / s).
  • L T / (2 xC).
  • the brightness of the corresponding point on the acoustic image is proportional to the amplitude value of the echo signal.
  • the echo signal modulates the radiance of the electron picture tube in a manner similar to the logarithmic transformation.
  • An ultrasonic probe that can perform electronic scanning includes a multi-element electroacoustic transducer (EAT) having a grid structure.
  • Each of the array elements 101 of the probe 100 is composed of a narrow strip of piezoelectric material with two electrodes 102, 103. Usually one of these electrodes is shared, Such as 103.
  • These array elements 101 are located on the surface of the relatively ultrasonically transparent film material, and the propagation speed of the ultrasonic waves in this material is less than that in the human body (about 1540 m / s).
  • On the other side of the EAT film material is a raised cylindrical shape 104.
  • This portion is in contact with the soft tissue of the human body.
  • This film acts as a small-aperture cylindrical acoustic convex mirror that focuses the acoustic emission onto the XY plane. If the electronic pulse reaches all of the elements of the electroacoustic transducer at the same time, the probe 100 will excite the cylindrical focus pulse. Since a small aperture lens is used in the probe 100, the length of the cylindrical focus area can be compared to the lens focus length.
  • an electronic delay line can be used to delay the time that the excited electron pulse reaches the array element for a certain time interval.
  • the electronic signals of the individual elements of the piezoelectric transducer are first delayed and then summed.
  • the selection principle of the delay amount is that the signal reflected at the focus F can be simultaneously reached at the entrance of the adder 202.
  • the focusing method of the present invention works in virtually the same way as a conventional acoustic convex mirror, and is therefore also referred to as an electronic convex mirror. Due to the fluctuating nature of the ultrasonic radiation, the focus of the electron convex mirror is not a point, but like a spotlight beam, its diameter increases as the focus moves away.
  • the transverse structure of the ultrasonic beam is similar to that of a conventional convex mirror, that is, the beam has a maximum at the center (main lobe) and a series of submaximum values (side lobes) on both sides. These side lobes seriously affect acoustics. The quality of the image.
  • the value of the side lobes can be attenuated by apodization. Specifically, it is implemented by multiplying the signals of the respective array elements by corresponding coefficients.
  • An important advantage of an electronic convex mirror is that the basic parameters can be changed easily and quickly without any mechanical movement of the probe element.
  • the electronic convex mirror can change the emission direction of the detection pulse and the focus area of the probe during the real-time operation of the instrument.
  • the depth of the measurement area propagates, and accordingly the echo source area is far from the probe.
  • the parameters of the convex mirror (focus position, aperture and apodization) can be changed in real time during echo signal reception.
  • the method of adjusting parameters in real time during the receiving process is called dynamic focus, dynamic aperture and dynamic apodization.
  • an existing ultrasound scanner typically includes five basic modules: a transmitter 301, a receiver 302, a control unit 303, a user interface unit 304, and a probe electronic multiplexer 305.
  • the scanner also includes a probe 100 (typically 1-6 probes).
  • the probe electronic multiplexer 305 ensures that different probes switch between the transmit circuit output and the receive circuit input.
  • Transmitter 301 is a unit that excites electronic detection pulses that pass through to the respective probe array elements and form an ultrasonic probe pulse.
  • Receiver 302 ensures amplification, discretization, digital filtering of the weak echo signals arriving from probe 100, and other processing required to form a focused beam in the receiving system.
  • Control unit 303 forms a set of signals for controlling all other modules to operate in accordance with a prescribed procedure.
  • the user interface unit 304 is for displaying the acoustic image on the screen of the monitor while receiving input from the control panel, the control unit 303 interpreting the instructions and converting them into control signals.
  • the probe electronic multiplexer 305 includes a set of electronic switches with control circuitry.
  • the array element currently using the probe is coupled to the output of the transmitter 301 and the input of the receiver 302 by a control signal from the control unit 303.
  • Transmitter 301 includes a multi-channel programmable digital pulse synthesizer having an output coupled to the control terminal of the output high voltage amplifier (one amplifier per array element) and an output formed at the output of transmitter 301.
  • the pulse synthesizer includes a set of identical probe pulse forming units, one for each array element. The same number of digital-to-analog converters as the channel have their inputs connected to the output of the sense pulse forming unit, and the output of the digital-to-analog converter forms the output of the synthesizer.
  • the enable input of the probe pulse forming unit is coupled to the universal input of the pulse synthesizer and forms the input of the transmitter 301.
  • the transmitter 301 operates as follows: When the pulse wave reaches the start input of the probe pulse forming unit, the digital signal formed is amplified by the high voltage amplifier and finally reaches the output of the transmitter 301.
  • Receiver 302 includes a set of low noise variable gain amplifiers, the same number of analog to digital converters And a dedicated processor.
  • the input of the low noise amplifier forms the input of the receiver 302, the output of which is connected to the input of the analog to digital converter.
  • the output of the analog-to-digital converter is coupled to the data input of the dedicated processor, and the data output of the processor forms the output of the receiver.
  • Receiver 302 operates in the following manner:
  • the analog signal entering from the input of receiver 30 2 is amplified by a low noise amplifier, discretized by an analog to digital converter, and placed in the memory of the dedicated processor.
  • the dedicated processor extracts data from the memory with a certain time delay, multiplies it by an apodization function, and adds the focus signal of the electron lens in this form. Further, the dedicated processor digitally filters, digitally detects the signal and then transmits the data to the output of the receiver 302.
  • Control unit 303 is a digital circuit that generates a clock synchronization signal for controlling other units of the device. It periodically transmits a signal that activates the transmitter 301, a signal that allows recording of the receiver 302 echo, and a signal that is ready for the user interface unit 304 data.
  • User interface unit 304 includes data post-processing nodes, information display devices that are sequentially connected; and a control panel with buttons and indicators.
  • the input of the data post-processing node forms the input of the data unit, while the input/output of the control panel 303 forms the input/output of the data control unit 304.
  • User interface unit 304 operates in the following form:
  • the data post-processing node converts the output digital signal of receiver 302 into a two-dimensional grayscale image, displayed on a rectangular grating plane.
  • the process of this transformation consists of at least two parts: First, the input signal is nonlinearly transformed point by point according to the law of logarithm or near logarithm (commonly referred to as Y-transformation).
  • the purpose of this conversion is to shift the dynamic range of the wide echo signal to the dynamic range that the monitor can display.
  • the digital signal formed corresponding to the sectoral ultrasound scan will be converted into a rectangular plane raster display (ie, digital scan conversion).
  • the image is displayed on the display.
  • the user operation interface unit 304 transfers the status information of the control panel to the control unit 3 0 3 and turns the indicator light on or off according to a command arriving from the control panel. Closest in U.S. Patent No. 5,685,308 describes a device in the present invention.
  • the existing medical ultrasonic diagnostic equipment has the following disadvantages:
  • the delay parameters of the transmitter and receiver should also be changed accordingly; while the parameters of the transmitter, receiver and other parameters of the existing detection device are fixed and cannot be changed; Transmitter, receiver - corresponding to a fixed multi-circuit, the probe can not adapt once it changes.
  • a primary object of the present invention is to provide a medical ultrasonic diagnostic apparatus which is controlled by a computer as its main control unit through a standard interface of a computer and an ultrasonic detecting device to realize high performance calculation and convenient parameter configuration.
  • Another object of the present invention is to provide a medical ultrasonic diagnostic apparatus in which parameters of a transmitter, a receiver, and the like can be flexibly set or changed, and adapted to accommodate any change in probe replacement.
  • the medical ultrasonic diagnostic apparatus of the present invention is composed of at least a computer as a main control unit and an ultrasonic detecting device; the computer is connected and interacted with the ultrasonic detecting device through its standard interface, and the computer passes Its standard interface transmits control signals to the ultrasonic detecting device and exchanges data for high performance calculation and convenient parameter configuration.
  • the ultrasonic detecting device further includes at least a controller, a transmitter, a receiver, and a probe; the local interface of the ultrasonic detecting device is respectively connected to the transmitter, the receiver, and the controller through a bus connection, and is used for controlling the computer. Signal transmission to the transmitter, receiver and control And causing the computer to perform number interaction with the transmitter, the receiver, and the controller; the probe is connected between the transmitter and the receiver, and receives the ultrasonic probe signal transmitted by the transmitter, and receives the detected object The probe returns a signal and transmits the probe return signal to the receiver.
  • the above transmitter is composed of an excitation pulse generator, a transmission data memory and a high voltage amplifier, wherein the excitation pulse generator is connected to the local interface through the bus, receives the control signal from the computer, and simultaneously takes out the storage delay from the transmission data memory.
  • the parameter controls the low-voltage transmitting pulse signal; the high-voltage amplifier receives the low-voltage transmitting pulse signal generated by the excitation pulse generator, amplifies it, and transmits it to the probe.
  • the receiver is composed of a preamplifier, a multi-channel analog switch, a variable gain amplifier, an analog-to-digital converter, and a data interface;
  • the preamplifier receives the return detection signal of the probe and amplifies it to a multi-channel analog switch.
  • the multi-channel analog switch outputs the signal to the variable gain amplifier for further amplification, and performs attenuation compensation, and then transmits it to the analog-to-digital converter. Performing analog-to-digital conversion; the digital signal subjected to analog-to-digital conversion is received and saved by the data interface;
  • the data interface is connected to the local interface through a bus, and the computer accesses and controls the data interface through the local interface.
  • a receive data memory is provided on the data interface for storing time delay parameters of the received data.
  • the receiver obtains the time delay parameter from the data memory to delay the corresponding signal.
  • the above computer can also set and/or modify the data in the data memory through the data interface.
  • the above controller is a synchronous controller, which is connected through a bus and a local interface for receiving The control signal of the computer, and under the action of the control signal, generates a synchronous control signal to control the clock and synchronization of the transmitter and the receiver, respectively.
  • the synchronization controller is also connected to a synchronous data memory for storing synchronization control parameters.
  • the above computer can also set and/or modify the data in the synchronous data storage by the controller.
  • the invention is implemented by a computer as its main control unit, and is connected with an ultrasonic detecting device through a standard interface of the computer, thereby realizing high performance calculation and convenient parameter configuration.
  • the transmitter, the receiver and the like of the present invention are respectively provided with corresponding data memories for storing their setting parameters. Once the parameters need to be changed, the corresponding settings can be made by the computer, and the setting or changing of the parameters is more flexible, and , adapted to any changes in the probe.
  • the data interface of the present invention adopts a serial design, and the increase in the number of probes does not cause a change in the entire device, thereby realizing flexible configuration of the probe.
  • Figure 1 is a linear probe barrel diagram of an electroacoustic transducer array on a ZX plane
  • Figure 2 is a simplified diagram of a linear probe of an electroacoustic transducer array on a YX plane;
  • Figure 3 is a linear probe barrel diagram of an electroacoustic transducer array on the YZ plane
  • Figure 4 is the simplest functional diagram of the test pulse transmitting and receiving ultrasonic beam electronic focusing
  • Figure 5 is a schematic block diagram of the existing product
  • Figure 6 is a schematic block diagram of a medical ultrasonic diagnostic apparatus of the present invention.
  • FIG. 7 is a schematic diagram of a circuit principle of a detecting device according to an embodiment of the present invention.
  • FIG. 8 is a circuit schematic diagram of a high voltage pulse amplifier in accordance with an embodiment of the present invention. detailed description
  • the present invention is composed of a computer 400 and an ultrasonic detecting device 500.
  • the computer 400 and the ultrasonic detecting device pass through a PCI interface (Per i phera l Component Interconnec ti on, peripheral component expansion interface) 600 connection communication, to achieve excitation pulse
  • the field programmable gate array (FPGA) device such as the data processor CTRL1, the data memory RM1 ... RM (K), the data processor RS, and the like, and loads the data stored in each.
  • the data processor RS After receiving the work instruction issued by the computer 406 through the PCI interface 407, the data processor RS automatically completes the work of the excitation pulse generator PCTRL, the data interface unit RBI... RB (K), and the multi-channel analog switch array IPS circuit. State control.
  • the data interface unit RBI-RB(K) is composed of an FPGA, and all time delay control data of the received data are stored in the data memories RM1...RM(K), respectively.
  • the excitation pulse generator PCTRL generates the front end of the excitation probe. The low-voltage pulse is amplified by high-voltage amplification HA1-HA(N), and the excitation element array elements El-E(N) (the number of array elements is N).
  • FIG. 8 is a schematic diagram of a high-voltage pulse amplifier.
  • the high-voltage amplifier consists of a P-type MOS transistor VT1 and an N-type MOS transistor VT2. Their drains are connected as high-voltage outputs, P-type MOS transistors VT1 and N-type MOS transistors VT2.
  • the sources are connected to positive and negative high voltage power supplies, and their gates are connected to the pulse excitation generator PCTRL through capacitors C1 and C2, respectively.
  • the array elements of the high-voltage generator circuit and the probe are - corresponding, but when a certain scan line of the image is formed, only some of the relevant excitation circuits participate in the work, and the remaining circuits are in an idle state, which is easily changed by a programming method. The number of incentive circuits involved in the work.
  • the ultrasonic echo signal reflected by the human body induces a weak electric signal on the array element El-E(N), which is transmitted to the preamplifier PA1...PA(N) for preamplification.
  • the number of preamplifiers and the number of probe elements are also—correspondingly. Not all echo signals are necessary when forming a certain scan line of the image. Generally, the nearest scan line is selected.
  • the echo signal is used to synthesize the signal of a certain scanning line. We can simply understand that the number of channels of the echo signal used to form a scanning line is the number of receiving channels.
  • the number of accepted channels is smaller than the number of probe arrays, and the preamplified signal is passed through the multi-channel analog switch IPS, so that the required signals are connected to the back-end circuit for further processing, and the remaining preamplifiers that are temporarily unused are disconnected, and all are completed.
  • the transformation of the receive channel of the signal When changing the position of the scan line, multi-way The analog switch is switched accordingly to change the access distribution of the preamplifier.
  • the input of the variable gain amplifier VA1...VA (M) is the output of the multi-channel analog switch, which further amplifies the signal and compensates for the attenuation of the ultrasonic wave as a function of depth.
  • the amplified analog signal is then digitally converted by an analog-to-digital converter ADC1...ADC (M).
  • the converted digital signal enters the data interface unit RB1...RBU) for serial addition of a certain delay law, and the delay amount of the added data is controlled by the data stored by the data memory leg 1...RM(K)
  • the control data in the data memory RM1 ... RMU) can be loaded by the computer 406, and the data interface units RB1 ... RB (K) are serially coupled, and the data is added.
  • the last added data enters the data processor RS, completes post-processing of the received data, and is stored in the data memory RMS. After the scanning of one frame of image is completed, a ready response is generated by the data processor RS to the PCI interface 407, and the computer receives the image data through the PCI interface 407, and further processes the obtained data, and then displays.
  • the computer 406 performs data loading on the excitation pulse generator (PCTRL) 501, the data memory RB1 ... RB (K), and the data processor RS circuit through the interface circuit, and the computer 406 does not process during the transmission and data reception of the formed image. Participating, and the data processor RS completes the control of the excitation pulse generator (PCTRL) 501, the data memory RB1 ... RB (K), and the data processor RS first sends a start pulse to the excitation pulse generator (PCTRL) 501 circuit.
  • the excitation pulse generator (PCTRL) 501 automatically generates an excitation pulse, and the correlation element emits only a single or several excitation pulses for one scan line instead of continuously operating.
  • the data processor RS After the completion of the transmission of all the relevant array elements, the data processor RS issues a start pulse to the data memories RB1...RB (K), and the receiving circuit starts receiving the echo signals. After receiving a scan line, the data processor RS repeats the above control, and the transmit and receive circuits automatically change the parameters used for the next scan line according to the configuration. After all the scan lines have been received, one frame of image data is obtained, and the data processor RS sends a work end signal to the computer 400 through the interface, requesting the computer 400 to read the data. When the computer 400 reads the data, it writes an instruction to continue processing to the data processor RS, and the data processor RS issues a reset signal to the excitation pulse generator PCTRL, the data memory RBI...

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  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Radar, Positioning & Navigation (AREA)
  • Remote Sensing (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Acoustics & Sound (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • General Physics & Mathematics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
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Abstract

La présente invention concerne un dispositif à ultrasons de diagnostic médical se composant d’au moins un ordinateur et d’un appareil de détection d’ultrasons. Sur l’appareil de détection d’ultrasons figurent également des interfaces locales pour raccorder et communiquer avec l’ordinateur, et l’ordinateur transmet des signaux de commande à l’appareil de détection d’ultrasons et procède à des échanges de données au travers de ses interfaces standard.
PCT/CN2005/000966 2005-07-04 2005-07-04 Dispositif à ultrasons de diagnostic médical WO2007003069A1 (fr)

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PCT/CN2005/000966 WO2007003069A1 (fr) 2005-07-04 2005-07-04 Dispositif à ultrasons de diagnostic médical

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2005/000966 WO2007003069A1 (fr) 2005-07-04 2005-07-04 Dispositif à ultrasons de diagnostic médical

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WO2007003069A1 true WO2007003069A1 (fr) 2007-01-11

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN105796131A (zh) * 2016-05-22 2016-07-27 复旦大学 背散射超声骨质诊断系统
WO2024032567A1 (fr) * 2022-08-12 2024-02-15 深圳迈瑞生物医疗电子股份有限公司 Circuit de transmission ultrasonore, appareil d'imagerie ultrasonore et procédé de génération de signal d'excitation

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6063030A (en) * 1993-11-29 2000-05-16 Adalberto Vara PC based ultrasound device with virtual control user interface
US6315731B1 (en) * 1999-03-31 2001-11-13 Olympus Optical Co., Ltd. Ultrasonic diagnostic apparatus capable of functional addition
US6530887B1 (en) * 1996-12-24 2003-03-11 Teratech Corporation Ultrasound probe with integrated electronics
CN1669530A (zh) * 2004-03-16 2005-09-21 北京天惠华数字技术有限公司 医用超声诊断设备

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6063030A (en) * 1993-11-29 2000-05-16 Adalberto Vara PC based ultrasound device with virtual control user interface
US6530887B1 (en) * 1996-12-24 2003-03-11 Teratech Corporation Ultrasound probe with integrated electronics
US6315731B1 (en) * 1999-03-31 2001-11-13 Olympus Optical Co., Ltd. Ultrasonic diagnostic apparatus capable of functional addition
CN1669530A (zh) * 2004-03-16 2005-09-21 北京天惠华数字技术有限公司 医用超声诊断设备

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN105796131A (zh) * 2016-05-22 2016-07-27 复旦大学 背散射超声骨质诊断系统
CN105796131B (zh) * 2016-05-22 2023-10-13 复旦大学 背散射超声骨质诊断系统
WO2024032567A1 (fr) * 2022-08-12 2024-02-15 深圳迈瑞生物医疗电子股份有限公司 Circuit de transmission ultrasonore, appareil d'imagerie ultrasonore et procédé de génération de signal d'excitation

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