KR102324390B1 - Portable Hybrid Ultrasonic Diagnostic Apparatus - Google Patents

Abstract

A portable hybrid ultrasound diagnosis apparatus according to the present invention includes an ultrasound probe; ultrasound image generator; and a power supply unit, wherein the ultrasound probe transmits a linear ultrasound signal from among the ultrasound signals to the subject in response to the high voltage pulse and receives a linear ultrasound echo signal reflected from the subject. piezoelectric element array; a second piezoelectric element array for transmitting a convex ultrasound signal from among the ultrasound signals to the subject in response to the high voltage pulse and receiving a convex ultrasound echo signal reflected from the subject; an array switch unit configured to switch an operation of any one of the first piezoelectric element array and the second piezoelectric element array in response to an operation control signal transmitted from the ultrasound image generating unit; and a multiplexer configured to perform a switching operation to output the high voltage pulse to selected piezoelectric elements among piezoelectric elements constituting the first piezoelectric element array or the second piezoelectric element array, wherein the operation control signal is and an operation mode selection signal for generating either linear scanning data corresponding to the first piezoelectric element array or convex scanning data corresponding to the second piezoelectric element array among the ultrasound image data.

Description

Portable Hybrid Ultrasonic Diagnostic Apparatus

The present invention relates to a portable ultrasound diagnosis apparatus, and more particularly, to a portable hybrid ultrasound diagnosis apparatus that can be used by switching to a linear type or a convex type.

The ultrasound diagnosis apparatus has non-invasive and non-destructive characteristics, and is widely used in the medical field to obtain information inside an object. The ultrasound diagnosis apparatus is very importantly used in the medical field because it can provide a doctor with a high-resolution image of the internal tissue of the object without the need for a surgical operation for directly incising and observing the object.

The ultrasound diagnosis apparatus is a device capable of irradiating an ultrasound signal from a body surface of a subject toward a target site in the body and extracting information from the reflected ultrasound signal to obtain an image of a soft tissue tomography or blood flow without invasiveness.

Compared with other imaging devices such as X-ray scanners, CT scanners (Computerized Tomography Scanner), MRI scanners (Magnetic Resonance ImageScanner), and nuclear medicine testing devices, ultrasound diagnostic devices are compact, inexpensive, and can be displayed in real time. Since there is no exposure to , X-rays, etc., it has the advantage of high safety, so it is widely used for diagnosis of the heart, abdominal organs, urinary and genital organs.

However, a conventional ultrasound diagnosis apparatus has a different structure for obtaining linear scanning data and a structure for obtaining convex scanning data, and a method of processing it is different from an ultrasound diagnosis apparatus for obtaining linear scanning data and convex scanning data. There was a problem in that an ultrasound diagnosis apparatus for acquiring .

Patent Publication No. KR 10-2012-0090470 (2012.08.17)

An object of the present invention is to provide a portable hybrid ultrasound diagnosis apparatus that enables mode conversion to a linear mode or a convex mode in order to acquire linear scanning data or convex ultrasound scanning data from ultrasound image data.

According to an aspect of the present invention, there is provided a portable hybrid ultrasound diagnosis apparatus comprising: an ultrasound probe configured to transmit an ultrasound signal to a subject and then receive an ultrasound echo signal reflected from the subject; To generate the ultrasound signal, a high voltage pulse is generated and output to the ultrasound probe, ultrasound image data corresponding to the ultrasound echo signal received by the ultrasound probe is generated, and the generated ultrasound image data is transmitted to a display device an ultrasound image generator; and a battery for charging and discharging electric power, and a power supply unit for supplying electric power for driving the ultrasonic image generator using the electric power charged in the battery, wherein the ultrasonic probe responds to the high voltage pulse a first piezoelectric element array which transmits a linear ultrasound signal from among the ultrasound signals to the subject and receives a linear ultrasound echo signal reflected from the subject; a second piezoelectric element array for transmitting a convex ultrasound signal from among the ultrasound signals to the subject in response to the high voltage pulse and receiving a convex ultrasound echo signal reflected from the subject; an array switch unit configured to switch an operation of any one of the first piezoelectric element array and the second piezoelectric element array in response to an operation control signal transmitted from the ultrasound image generating unit; and a multiplexer configured to perform a switching operation to output the high voltage pulse to selected piezoelectric elements among piezoelectric elements constituting the first piezoelectric element array or the second piezoelectric element array, wherein the operation control signal is and an operation mode selection signal for generating either linear scanning data corresponding to the first piezoelectric element array or convex scanning data corresponding to the second piezoelectric element array among the ultrasound image data.

The first piezoelectric element array and the second piezoelectric element array each face a front direction and are arranged in parallel with each other in a linear form.

The ultrasound image generating unit may include: a pulse generating module configured to generate an electrical high voltage pulse of any one of the linear ultrasound signal and the convex ultrasound signal according to the operation mode selection signal; a signal processing module for amplifying the amplitude of any one of the linear ultrasonic echo signal and the convex ultrasonic echo signal and converting it into a digital signal;

a transceiver module for transmitting the high voltage pulse generated by the pulse generating module to the ultrasonic probe, or for receiving the linear ultrasonic echo signal or the convex ultrasonic echo signal from the ultrasonic probe and transmitting it to the signal processing module; cause the pulse generating module to generate the high voltage pulse corresponding to the ultrasonic probe, and the linear scanning data corresponding to the first piezoelectric element array or the second piezoelectric element according to the digital signal converted by the signal processing module a beamforming module that generates the convex scanning data corresponding to the array; a processing module controlling the beamforming module to perform beamforming corresponding to the ultrasound probe and transmitting the ultrasound image data received from the beamforming module to the display device; and a communication module connected to the display device through a communication network to transmit the linear scanning data or the convex scanning data.

The beamforming module is configured to generate a high voltage pulse corresponding to linear beamforming by calculating a delay value of an ultrasonic velocity or a correction value according to steering according to the operation mode selection signal for generating the linear scanning data. characterized by processing.

The beamforming module may generate a high voltage pulse for virtual convex beamforming according to a distance between the ultrasound probe and the subject according to the operation mode selection signal for generating the convex scanning data.

The processing module generates ultrasound image data corresponding to the linear scanning data generated by the beamforming module using a linear scanning conversion algorithm, and uses a convex scanning conversion algorithm to perform the convex scanning generated by the beamforming module and generating ultrasound image data corresponding to the data.

The processing module may control the beamforming module by generating the operation mode selection signal according to a linear operation mode command or a convex operation mode command generated by the display device and transmitted through the communication module.

According to the present invention, in order to obtain linear scanning data or convex ultrasound scanning data from among ultrasound image data, by enabling mode conversion to a linear mode or a convex mode, there are two types of obtaining linear scanning data or convex scanning data. Linear ultrasound image data or convex ultrasound image data may be acquired through one ultrasound probe without using an ultrasound probe. Accordingly, it is possible to easily obtain linear ultrasound image data or convex ultrasound image data by using one ultrasound diagnosis apparatus depending on the situation, and in terms of cost, it is possible to obtain a cost saving effect of not having a plurality of devices having different functions. .

1 is a block diagram of a portable hybrid ultrasound diagnosis apparatus according to an embodiment of the present invention.
FIG. 2 is a block diagram of an embodiment for explaining the ultrasound probe shown in FIG. 1 .
FIG. 3 is a structural diagram of an embodiment for explaining the ultrasound probe shown in FIG. 1 .
FIG. 4 is a block diagram illustrating an ultrasound image generator illustrated in FIG. 1 according to an exemplary embodiment.
5 is a reference diagram for explaining a beamforming calculation process in a linear mode.
6 is a reference diagram for explaining a beamforming calculation process in a convex mode.
7 is a reference diagram for explaining a beamforming calculation process in a phased-array mode.
8 is a reference diagram for explaining a beamforming calculation process in a Curve-Phased-Array mode.
9 is a reference diagram for explaining a beamforming calculation process in a virtual convex mode.
10 is a reference diagram illustrating an angle between a center point of the ultrasound probe 100 and an element.
11 is a schematic diagram of the total distance along the Scanline.
12 is a reference diagram for explaining a near field and a far field of ultrasound.
13 is a reference diagram illustrating an Rx beamforming flow diagram.
14 is a reference diagram illustrating an Rx beamforming calculation method.
15 is a reference diagram illustrating an Rx beamforming summation timing diagram.
16 is a reference diagram illustrating an Rx beamforming summation data flow diagram.
17 is a reference diagram illustrating a beamforming calculation according to characteristics of a PA structure.
18 is a reference diagram illustrating a signal processing implementation flow according to characteristics of a PA structure.
19 is a reference graph for explaining a linear beamforming delay.
20 is a reference graph for explaining a Tx beamforming simulation in a phased mode.
21 is a reference graph for explaining a Tx beamforming simulation in a virtual convex mode.
22 is a reference graph for explaining a linear type Rx beamforming simulation.
23 is a reference graph for explaining a phased-type Rx beamforming simulation.
24 is a reference graph for explaining an Rx simulation of a virtual convex type.
25 is a reference diagram for explaining a linear type Scan Conversion output map.
26 is a diagram illustrating Matlab code for creating a memory map.
27 is a reference diagram showing a test pattern for simulation.
28 is a reference diagram for explaining Pixel Interpolation.
29 is a reference diagram illustrating a linear type Scan Conversion Image.
30 is a reference diagram for explaining a scan conversion map of a virtual convex type.
31 is a reference diagram illustrating Matlab code for creating a memory map.
32 is a reference diagram illustrating a test pattern for simulation.
33 is a reference diagram for explaining Pixel Interpolation.
34 is a reference diagram illustrating a Virtual Convex Type Scan Conversion Image.
35 is a reference diagram for explaining a Sector type Scan Conversion output map.
36 is a reference diagram illustrating Matlab code for creating a memory map.
37 is a reference diagram for explaining a test pattern for simulation.
38 is a reference diagram illustrating Pixel Interpolation.
39 is a reference diagram illustrating a Sector Type Scan Conversion Image.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.

The embodiments of the present invention are provided to more completely explain the present invention to those of ordinary skill in the art, and the following embodiments can be modified in various other forms, and the scope of the present invention is not limited. It is not limited to the following examples. Rather, these examples are provided so that this disclosure will be more thorough and complete, and will fully convey the spirit of the invention to those skilled in the art.

The terminology used herein is used to describe specific embodiments, not to limit the present invention. As used herein, the singular form may include the plural form unless the context clearly dictates otherwise. Also, as used herein, "comprise" and/or "comprising" specifies the presence of the recited shapes, numbers, steps, actions, members, elements, and/or groups thereof. , does not exclude the presence or addition of one or more other shapes, numbers, operations, members, elements and/or groups. As used herein, the term “and/or” includes any one and any combination of one or more of those listed items.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, embodiments of the present invention will be described with reference to drawings schematically illustrating embodiments of the present invention. In the drawings, variations of the illustrated shape may be expected, for example depending on manufacturing technology and/or tolerances. Accordingly, embodiments of the present invention should not be construed as limited to the specific shape of the region shown herein, but should include, for example, changes in shape caused by manufacturing.

1 is a block diagram of a portable hybrid ultrasound diagnosis apparatus 10 according to an embodiment of the present invention.

Referring to FIG. 1 , a portable hybrid ultrasound diagnosis apparatus 10 according to an embodiment of the present invention includes an ultrasound probe 100 , an ultrasound image generation unit 200 , and a power supply unit 300 .

The ultrasound probe 100 transmits an ultrasound signal to the subject, and then receives an ultrasound echo signal reflected from the subject. Specific details of the ultrasound probe 100 will be described later.

The ultrasound image generator 200 generates a high voltage pulse to generate an ultrasound signal and outputs it to an ultrasound probe, generates ultrasound image data corresponding to the ultrasound echo signal received from the ultrasound probe, and generates the ultrasound image data. to the display device. Specific details of the ultrasound image generator 200 will be described later.

The power supply unit 300 supplies power for driving the ultrasound image generation unit 200 and/or the ultrasound probe 100 . To this end, the power supply unit 300 includes a battery for charging and discharging power, and provides operating power of the ultrasound image generator 200 and/or the ultrasound probe 100 using the power charged in the battery.

FIG. 2 is a block diagram of an embodiment for explaining the ultrasound probe 100 shown in FIG. 1 . Also, FIG. 3 is a structural diagram of an embodiment for explaining the ultrasound probe 100 shown in FIG. 1 .

Referring to FIG. 2 , the ultrasound probe 100 includes a first piezoelectric element array 110 , a second piezoelectric element array 120 , an array switch unit 130 , and a multiplexer 140 .

The first piezoelectric element array 110 transmits a linear ultrasound signal among ultrasound signals to the subject, and receives a linear ultrasound echo signal reflected from the subject.

The first piezoelectric element array 110 includes piezoelectric elements formed of a piezoelectric material. The piezoelectric material vibrates to generate a pulse of sound waves, which is transmitted into the human body, and receives the reflected echo and converts it into an electrical signal. Recently, piezoelectric ceramic lead zirconatetitante (PZT), which has the best electroacoustic conversion efficiency, is mainly used as a piezoelectric material. The first piezoelectric element array 110 is generally configured such that a large number of piezoelectric elements such as 64, 128, or 192 are arranged in an array form. At this time, the range of the electric pulse driving the piezoelectric element uses a high voltage of +100V to -100V.

The second piezoelectric element array 120 transmits a convex ultrasound signal among ultrasound signals to the subject, and receives a convex ultrasound echo signal reflected from the subject.

The second piezoelectric element array 120 also includes piezoelectric elements formed of a piezoelectric material. The second piezoelectric element array 120 is also configured such that a large number of piezoelectric elements such as 64, 128, 192 are arranged in an array form. In this case, the second piezoelectric element array 120 may also use a high voltage of +100V to -100V in the range of the electric pulse for driving the piezoelectric element.

The first piezoelectric element array 110 and the second piezoelectric element array 120 each face a front direction, and are arranged in parallel with each other in a linear form.

Referring to FIG. 3 , it can be seen that in the first piezoelectric element array 110 and the second piezoelectric element array 120 , a plurality of piezoelectric elements are arranged in parallel in a linear form toward the front. In particular, the structure of the second piezoelectric element array 120 is a structure for transmitting a convex ultrasound signal to a subject and receiving a convex ultrasound echo signal reflected from the subject. have This is to maintain the same external shape as the first piezoelectric element array 110 . The array structure of the second piezoelectric element array 120 is a line type, and in order to input and output a convex ultrasound signal or a convex ultrasound echo signal under this structure, a beam suitable for a line type structure in the beamforming module 250 as will be described later. A forming process is required. This will be described later.

The array switch unit 130 switches the operation of any one of the first piezoelectric element array 110 and the second piezoelectric element array 120 in response to the operation control signal transmitted from the ultrasound image generating unit 200 .

The operation control signal selects an operation mode for generating either linear scanning data corresponding to the first piezoelectric element array 110 or convex scanning data corresponding to the second piezoelectric element array 120 among the ultrasound image data. contains signals. The operation mode selection signal is an operation control signal generated and transmitted by the ultrasound image generator 200 .

The multiplexer 140 performs a switching operation to output a high voltage pulse to selected piezoelectric elements among the piezoelectric elements constituting the first piezoelectric element array 110 or the second piezoelectric element array 120 .

The multiplexer 140 serves to reduce the number of signal pins, and a signal between the piezoelectric elements constituting the first piezoelectric element array 110 and the second piezoelectric element array 120 and the transmission/reception module 210 . Match the number of lines. That is, when transmitting an ultrasonic signal and receiving an ultrasonic echo signal, all piezoelectric elements in the first piezoelectric element array 110 or the second piezoelectric element array 120 are not used at the same time, but some piezoelectric elements located at a position to collect ultrasonic echo data In order to use only the elements, the corresponding piezoelectric elements are electrically selected and connected to the transmission/reception module 210 . For example, the number of piezoelectric elements of the first piezoelectric element array 110 or the second piezoelectric element array 120 may be 64, 128, 192, etc., respectively, and the number of signal lines by the operation of the multiplexer 140 can be optionally adjusted.

FIG. 4 is a block diagram of an embodiment for explaining the ultrasound image generator 200 shown in FIG. 1 .

Referring to FIG. 4 , the ultrasound image generating unit 200 includes a transceiver module 210 , a pulse generating module 220 , a signal processing module 230 , a beamforming module 240 , a processing module 250 , and a communication module ( 260).

The transmission/reception module 210 transmits the high voltage pulse generated by the pulse generating module 220 to the ultrasound probe 100 or an analog signal transmitted from the ultrasound probe 100 to the signal processing module 230 .

In particular, the transceiver module 210 transmits a high voltage pulse for outputting a linear ultrasound signal or a convex ultrasound signal to the ultrasound probe 100 , or receives a linear ultrasound echo signal or a convex ultrasound echo signal from the ultrasound probe 100 . It is transferred to the processing module 230 .

The pulse generating module 220 generates an electric pulse applied to the first piezoelectric element array 110 or the second piezoelectric element array 120 to generate ultrasonic waves. In particular, the pulse generating module 220 generates an electric high voltage pulse of any one of a linear ultrasonic signal and a convex ultrasonic signal according to the operation mode selection signal.

The signal processing module 230 amplifies and converts the ultrasonic echo signal returned from the subject to a digital signal because the size is very small. In particular, the signal processing module 230 amplifies the signal size of any one of the linear ultrasonic echo signal and the convex ultrasonic echo signal and converts it into a digital signal.

The beam forming module 240 causes the pulse generating module 220 to generate a high voltage pulse corresponding to the ultrasonic probe 100 , and according to the digital signal converted by the signal processing module 230 , the first piezoelectric element array 110 . ) or convex scanning data corresponding to the second piezoelectric element array 120 are generated.

Making the pulse generating module 220 generate a suitable high voltage pulse using parameters suitable for the ultrasound probe 100 is called TX beamforming, which focuses the energy of the ultrasound at a focal point at a specific distance when transmitting the ultrasound. It means to delay the time of the electric pulse according to the position of the piezoelectric element in order to In addition, receiving the digital signal converted by the signal processing module 230, performing data conversion so as to be matched with the ultrasonic probe 100, and transferring the data to the processing module 250 is called RX beamforming, which is an ultrasonic echo signal When receiving , the electric signal from each piezoelectric element is delayed according to the position and reception time of the piezoelectric element, and the time-delayed signals are summed to generate ultrasonic data.

The beamforming module 240 calculates a delay value of an ultrasonic velocity or a correction value according to steering according to the operation mode selection signal for generating linear scanning data to generate a high voltage pulse corresponding to linear beamforming. handle In addition, the beamforming module 240 processes to generate a high voltage pulse for virtual convex beamforming according to a distance between the ultrasound probe and the subject according to the operation mode selection signal for generating convex scanning data.

The beamforming module 240 performs the following operations as Tx beamforming.

Since the piezoelectric elements are structurally fixed, in addition to structural focusing, the beamforming module 240 performs the following calculation process for processing the focusing signal as Tx beamforming.

5 is a reference diagram for explaining a beamforming calculation process in a linear mode.

1) The beamforming calculation process in the linear mode is as follows.

Step 1: Obtain the x-axis value from the center to the element (piezoelectric element) distance.

Step 2: Find the z-axis distance by depth.

Step 3: Find the hypotenuse length using the Pythagorean theorem.

Step 4: Find a delay value based on frequency and ultrasonic speed.

2) The steering process in the linear mode is as follows.

Step 1: Find the x-coordinate of the point steered by 15[degrees] from the center.

x1=depth*tan15 [degrees]

Step 2: Compensate as much as the position of the piezoelectric element.

x= x1 + x2

Step 3: Find the hypotenuse length using the Pythagorean theorem.

Step 4: Find a delay value based on frequency and ultrasonic speed.

delay = (hypotenuse*Fs)/sonic velocity

6 is a reference diagram for explaining a beamforming calculation process in a convex mode. The beamforming calculation process in the convex mode is as follows.

Step 1: Find r_x using a trigonometric function.

r=50, x: trigonometric formula, r_x=r*cos(theta*pi/180)-r

Step 2: Find the hypotenuse of the focal point and the triangle of the element.

hypotenuse = Pythagorean theorem

x= (depth +r_x), y=r*sin(theta*pi/180)

7 is a reference diagram for explaining a beamforming calculation process in a phased-array mode. The beamforming calculation process in the phased-array mode is as follows.

Step 1: Find x1 using theta that fits the line.

x1=depth*sin(theta*pi/180)

x3=x1 + x2

Step 2: Find z.

z=depth*cos(theta*pi/180)

Step 3: Find the length of the hypotenuse.

r_n=Pythagorean theorem

Step 4: Find the delay value with frequency and ultrasonic speed.

delay=(hypotenuse*Fs)/ultrasonic velocity

8 is a reference diagram for explaining a beamforming calculation process in a Curve-Phased-Array mode. The calculation process in Curve-Phased Array mode is as follows.

Step 1: Find x1 using theta that fits the line.

x1=depth*sin(theta*pi/180)

x3=x1 + x2 - x4

Step 2: Find z.

z=(depth*cos(theta*pi/180)) - z2

Step 3: Find the length of the hypotenuse.

r_n=Pythagorean theorem

Step 4: Find the delay value with frequency and ultrasonic speed.

delay=(hypotenuse*Fs)/ultrasonic velocity

9 is a reference diagram for explaining a beamforming calculation process in a virtual convex mode. FIG. 10 is a reference diagram illustrating an angle between a center point of the ultrasound probe 100 and an element, and FIG. 11 is a schematic diagram of a total distance along a scanline.

The calculation process in Virtual Convex mode is as follows.

Step 1: Find the distance of the elements from the reference point.

Known Information: Defined angle value, element pitch value

ex) pitch = 0.3 angle = 15°N_sl= 128

Second step: The height is obtained from the pitch information of the center element of sc0.

Ex) Element_mm = ((-N_sl*0.5+0.5)*pitch + (0:1:N_sl-1)*pitch)

Step 3: Find the base of the triangle.

tan(angle) = b/a = b / element_lenth

)는 밑변 / 높이의 비율이다.tan(

) is the ratio of base/height.

)로 나누면 밑변을 알 수 있다.I know the height as pitch information, so I set the height to tan(

) to find the base.

Step 4: Find the hypotenuse using the base and the height.

Hypotenuse = SQRT(base^2 + height^2)

Element_radius_sc (index_sc, 1) = sqrt (Element_mm(index_sc, 1)^2 + Center_Radius^2)

Step 5: Since the center of the ultrasound probe and the angle of each scan line are different, the angle of each scan line of the element needs to be calculated again.

Element_angle_sc(index_sc,1) = acosd(Center_Radius/Element_radius_sc)

Step 6: Find the total distance of the scan line.

focal_depth + element_radius_sc = sc_total_r

Step 7: Find Focus_x_sc by using the angle according to the position of the element.

Focus_x_sc = sc_total_r * sind (Element_angle_sc)

Step 8: Find the x value from the ultrasonic probe to the focal point.

current_x = Focus_x_sc - current_element_x

Step 9: Find the base using the focal depth.

focus_z = focal_depth * cosd (Element_angle_sc)

Step 10: Find the hypotenuse using the base and the height.

current_delay = SQRT( current_x^2 +focus_z^2)

Step 11: Divide the ultrasonic speed and frequency.

my_delay = current_delay *Fs / SoundSpeed

12 is a reference diagram for explaining a near field and a far field of ultrasound.

The region for each frequency according to the NFL (Near Field Length) is defined as the Near Field Length as the region until the ultrasonic wave travels in diameter up to a certain distance until it is emitted. Near field length for each frequency becomes longer as the frequency increases, and it varies depending on the mode.

The attenuation coefficient and attenuation rate of the ultrasonic signal will be described as follows.

Table 1 is a table showing the damping coefficient.

Relative intensity (dB) Intensity remaining in the reflected beam % lost robber 0 1/1 100 0 -One 1/1.26 79 21 -2 1/1.6 63 37 -3 1/2 50 50 -6 1/4 25 75 -10 1/10 10 90 -20 1/100 One 99 -30 1/1000 0.1 99.9 -40 1/10000 0.01 99.99

Table 2 is a table showing the attenuation coefficient for living tissue.

medium Attenuation factor (dB/cm) at 1 MHz water 0.0002 blood) 0.2 soft tissue 0.5 fat 0.6 liver 0.7 adult brain 0.8 kidney 1.0 muscle 1.5 bone 10 lung 41

Attenuation rate for each soft tissue frequency

2MHz : 30dB / Soft tissue attenuation coefficient 0.5 * Frequency 2 = 30 cm

3.5MHz : 30dB / Soft tissue attenuation coefficient 0.5 * Frequency 3.5 = 17 cm

4MHz : 30dB / Soft tissue attenuation coefficient 0.5 * Frequency 4 = 15cm

5MHz : 30dB / Soft tissue attenuation coefficient 0.5 * Frequency 5 = 12cm

6MHz : 30dB / Soft tissue attenuation coefficient 0.5 * Frequency 6 = 10cm

7.5MHz : 30dB / Soft tissue attenuation coefficient 0.5 * Frequency 7.5 = 8cm

9 MHz: 30dB / soft tissue attenuation coefficient 0.5 * frequency 9 = 6.6cm

10 MHz : 30dB / Soft tissue attenuation coefficient 0.5 * Frequency 10 = 6cm

Since the beamforming module 240 can estimate the limitation of beamforming according to attenuation of the near field length and frequency, it performs Tx beamforming design reflecting this.

The beamforming module 240 performs the following operations as Rx beamforming.

13 is a reference diagram illustrating an Rx beamforming flow diagram.

The ultrasonic wave arrives later than the ultrasonic wave emitted from elements that are close to the focal point, and the same time difference occurs in receiving the reflected wave. Tx sets the focal point and fires for a moment, but Rx is calculated by looking at the input signal for each sample as the focal point.

The Rx signal is transmitted as an input to the transducer with a time difference depending on the focal point position. After removing noise from the input signal through the Low Noise Amplifier (LNA), an appropriate gain is given through the Variable Gain Amplifier (VGA) to adjust the signal level.

By attenuating frequencies higher than the Nyquist frequency, it passes through the Anti Aliasing Filter (AAF) to prevent aliasing elements from being collected. The previously analog signal is converted into a digital signal through the Analog Digital Converter (ADC). It shows the flow of outputting signals suitable for delay through FIFO and summing them.

It shows the order of input from the target to the transducer. Inputs are passed from the nearest Array, and they must be stored in the order in which they were entered. It is stored to wait for a signal coming in late from a distance, and the delay calculation is calculated according to the sampling frequency by dividing the difference according to the array distance from the first input signal to the ultrasonic speed.

14 is a reference diagram illustrating an Rx beamforming calculation method, FIG. 15 is a reference diagram illustrating an Rx beamforming summation timing diagram, and FIG. 16 is a reference diagram illustrating an Rx beamforming summation data flow diagram.

This is a simplified process of receiving continuous input data and creating one line data by summing the data in the memory or register stored for each calculated delay. Also, the axial resolution increases according to the sampling rate, and the sample rate limit can be compensated for by interpolation between the sampling rates.

Rx beamforming in the phased array mode will be described as follows.

17 is a reference diagram illustrating a beamforming calculation according to characteristics of a PA structure, and FIG. 18 is a reference diagram illustrating a signal processing implementation flow according to characteristics of a PA structure.

The sin(theta) and cos(theta) values are stored in memory, and fixed values are calculated according to the set depth during Tx operation. The picth information of the elements is defined as a parameter, and it can be confirmed that there is the largest delay in SQRT.

Matlab simulation verification for the aforementioned beamforming algorithm is as follows.

1) Tx beamforming simulation verification

Simulation is conducted based on Tx Frequency 180MHz, focal point 10 ~ 100mm, Sound Speed 1540m/s, 128 Scanline, 128 element, 24 channel, 0.3mm element pitch.

19 is a reference graph for explaining the linear beamforming delay, FIG. 20 is a reference graph for explaining the Tx beamforming simulation (10 mm left, 100 mm right) in the phased mode, and FIG. 21 is Tx beamforming in the virtual convex mode It is a reference graph for explaining the simulation (left 10mm, right 100mm).

2) Rx beamforming simulation verification

Simulation is performed based on Rx Frequency 45MHz, Sound Speed 1540m/s, 128 Scanline, 128 element, 24 channel, 0.3mm element pitch.

22 is a reference graph for explaining a linear type Rx beamforming simulation (10, 50, 100 mm from the left), and FIG. 23 is a reference graph for explaining a phased type Rx beamforming simulation (10, 50, 100 mm from the left) It is a reference graph, and FIG. 24 is a reference graph for explaining the virtual convex type Rx simulation (10, 50, and 100 mm from the left).

The processing module 250 controls the beamforming module 240 to perform beamforming corresponding to the ultrasound probe 100 , and transmits ultrasound image data received from the beamforming module 240 to a display device (not shown). control to transmit.

The processing module 250 transmits the ultrasound scan data to a display device (not shown) through the communication module 260 or performs a function of controlling the entire system. In addition, in order to reduce the bandwidth of a transmission line used for communication, scan data is compressed when necessary.

In this case, the processing module 250 generates linear ultrasound image data corresponding to the linear scanning data generated by the beamforming module 240 using a linear scanning conversion algorithm, and uses a convex scanning conversion algorithm to generate the beamforming module 240 ) to generate convex ultrasound image data corresponding to the convex scanning data generated in FIG. The processing module 250 controls the beamforming module by generating the operation mode selection signal according to a linear operation mode command or a convex operation mode command generated by the display device and transmitted through the communication module.

The processing module 250 performs a linear scanning algorithm, and scan conversion is performed according to an actual transmitting/receiving beamforming algorithm. In particular, since what comes out of the Rx beamforming result is loaded into the actual memory map, when interpolation is performed, the scan line and sample location of the original data are properly found by referring to the original data. pay

25 is a reference diagram for explaining a linear type Scan Conversion output map, FIG. 26 is a diagram illustrating Matlab code for making a memory map, and FIG. 27 is a reference diagram illustrating a test pattern for simulation.

In the linear type, scan line data is generated where the element exists, so the image is reconstructed as much as the element size. When predicting DSC results through computer simulation, the conditions of image data are as follows.

Scan line: 128, Sample Data 1024

A total of three types of test patterns are mapped to memory.

Case I : Axial direction

Case II: Lateral direction

Case III : Axail + Lateral direction data

The data value is a memory map in which the brightness values of Black (0) and White value (255) are repeated.

The ultrasonic probe type used in the simulation can be tested with a linear probe having 128 elements.

Ultrasonic probe conditions: element 128, pitch 0.3

Common condition: View Depth to obtain scan data is 60mm, and scan conversion output image has 512 by 512 pixels.

The scan conversion algorithm for the linear type is as follows.

Calculate screen pixel distance on the monitor ( x-axis: dx , y-axis: dy )

Current Pixel Distance = View Depth / Display Pixel number

The distance per pixel is calculated by dividing 512 by 512, which is the number of display pixels based on the currently scanned View Depth. (The pixel distance on the x-axis and y-axis is the same, and is calculated as the actual distance.)

Compute the scan line position and sample position in real memory relative to the current pixel position (distance coordinates) to be displayed.

Original Scan line position = Current Display X distance / ( Probe Aperture Size / Scan line number )

The scan line position in the memory is calculated by dividing the current pixel distance by the probe size divided by the total number of scan lines.

Original Depth position = Current Display Y distance / Memory Sample distance

The sample location in the memory is calculated by dividing the distance of the current pixel by the distance between samples in the memory.

How to fill the current pixel to display with values (bilinear interpolation method)

28 is a reference diagram for explaining Pixel Interpolation, and FIG. 29 is a reference diagram illustrating a linear type Scan Conversion Image.

The summary of calculating the final interpolation point for the variables is as follows.

P = ( 1 - dx) * ( 1 - dy ) * P00 + (1 - dy ) * dx * P10 + dy * ( 1-dx) * P01 + dx * dy * P11

P : interpolation point, dx : Distance between left scanlines, dy : Distance between upper samples, P00 : Memory value at left top, P10 : Memory value at right top, P01 : Memory value at left bottom, P11 : memory value in the right bottom

It can be seen that the linear type scan conversion output image is expressed according to the actual transmission/reception structure in the memory map.

The virtual convex scan algorithm and simulation will be described as follows.

30 is a reference diagram illustrating a virtual convex type scan conversion map, FIG. 31 is a reference diagram illustrating Matlab code for making a memory map, and FIG. 32 is a reference diagram illustrating a test pattern for simulation.

Scan conversion follows the actual transmission/reception beamforming algorithm as it is. In particular, since the output from the Rx beamforming result is loaded into the actual memory map, it is necessary to find the scan line position and sample position of the original data by referring to the original data during interpolation.

In the virtual convex type, since scan line data is generated to transmit and receive at a virtual location like the convex type, the image is reconstructed by the FOV angle. It is possible to predict the DSC results through computer simulation.

The condition of image data is as follows.

Scan line: 128, Sample Data 1024

A total of three types of test patterns are mapped to memory.

Case I : Axial direction

Case II: Lateral direction

Case III : Axail + Lateral direction data

The data value is a memory map in which the brightness values of Black (0) and White value (255) are repeated.

The probe type used for the simulation is a linear ultrasonic probe with 128 elements. Linear ultrasonic probe conditions: element 128, pitch 0.3, maximum Steer Angle 15 degree, FOV 30 degree

The scan conversion algorithm for the virtual convex type is as follows.

33 is a reference diagram for explaining Pixel Interpolation, and FIG. 34 is a reference diagram illustrating a Virtual Convex Type Scan Conversion Image.

Calculate screen pixel distance on the monitor ( x-axis: dx , y-axis: dy )

Current Pixel Distance = View Depth / Display Pixel number

The distance per pixel is calculated by dividing 512 by 512 by 512, which is the number of display pixels based on the currently scanned View Depth (the pixel distance on the x-axis and y-axis is the same, calculated as the actual distance).

Calculate the actual memory scan line position and sample position for the current pixel position to be displayed.

Original Scan line position = Current Display X distance / ( Probe FOV angle / Scan line number )

The scan line position in the memory is calculated by dividing the current pixel distance by the probe size divided by the total number of scan lines.

Original Depth position = Current Display Y distance / Memory Sample distance

The sample location in memory is calculated by dividing the distance of the current pixel by the distance between samples in memory.

How to pad values into the current pixel to be displayed (bilinear interpolation method)

The summary of calculating the final interpolation point for the variables is as follows.

P = ( 1 - dx) * ( 1 - dy ) * P00 + (1 - dy ) * dx * P10 + dy * ( 1-dx) * P01 + dx * dy * P11

It can be seen that the virtual convex type scan conversion output image is expressed according to the actual transmission/reception structure in the memory map.

The Sector Scan algorithm and simulation will be described as follows.

35 is a reference diagram for explaining a Sector type Scan Conversion output map. FIG. 36 is a reference diagram illustrating Matlab code for creating a memory map, and FIG. 37 is a reference diagram for explaining a test pattern for simulation.

Scan conversion follows the actual transmission/reception beamforming algorithm as it is. In particular, since the output from the Rx beamforming result is loaded into the actual memory map, it is necessary to find the scan line position and sample position of the original data by referring to the original data during interpolation.

In the sector type, scan line data is generated by steering the ultrasound beam at the center of the element, so the image is reconstructed as much as Min and Max Steer Angle. When predicting DSC results through computer simulation, the conditions of image data are as follows.

Scan line: 128, Sample Data 1024

A total of 3 types of test patterns are mapped to memory

Case I : Axial direction

Case II: Lateral direction

Case III : Axail + Lateral direction data

The data value is a memory map in which the brightness values of Black (0) and White value (255) are repeated.

The probe type used for simulation is a linear probe with 128 elements. Probe condition: element 64, pitch 0.24, FOV (Field of View) 60 degree

The scan conversion algorithm for sector type is as follows.

38 is a reference diagram illustrating Pixel Interpolation, and FIG. 39 is a reference diagram illustrating Sector Type Scan Conversion Image.

Calculate screen pixel distance on the monitor ( x-axis: dx , y-axis: dy )

Current Pixel Distance = View Depth / Display Pixel number

The distance per pixel is calculated by dividing 512 by 512, which is the number of display pixels based on the currently scanned View Depth.

Calculate the scan line location and sample location of the actual memory for the current pixel location to be displayed.

Original Scan line position = Current Display X distance / ( Probe FOV angle / Scan line number )

The scan line position in the memory is calculated by dividing the current pixel distance by the probe size divided by the total number of scan lines.

Original Depth position = Current Display Y distance / Memory Sample distance

The sample location in memory is calculated by dividing the distance of the current pixel by the distance between samples in memory.

How to fill the current pixel for display with values (bilinear interpolation method)

The summary of calculating the final interpolation point for the variables is as follows.

P = ( 1 - dx) * ( 1 - dy ) * P00 + (1 - dy ) * dx * P10 + dy * ( 1-dx) * P01 + dx * dy * P11

P : interpolation point, dx : Distance between left scanlines, dy : Distance between upper samples, P00 : Memory value at left top, P10 : Memory value at right top, P01 : Memory value at left bottom, P11 : memory value in the right bottom

It can be seen that the sector type scan conversion output image is expressed according to the actual transmission/reception structure in the memory map.

The communication module 260 transmits/receives data to and from the display device to generate and transmit ultrasound image data. The communication module 260 is a communication module that transmits and receives data to and from an external electronic device. The communication module 260 may use a wired/wireless communication method. As the wired communication method, a wired cable such as a USB cable may be used, and a wireless communication method may be used. For example, it may be a module using one of Bluetooth, Wireless USB, Wireless LAN, WiFi, Zigbee, or Infrared Data Association (IrDA), which is infrared communication.

The communication module 260 may transmit the ultrasound image generated under the control of the processing module 250 to the display device. In this case, the display device may be a PC, a smartphone, a tablet-type device, a pad-type device, a PDA, or the like.

Such a display device may include a data communication unit for performing data communication, a menu input unit for receiving a menu signal from a user, a screen display unit for displaying an ultrasound image and a menu, and a control unit for exchanging control signals with the processing module 250 . .

At this time, the data communication unit of the display device receives the scan data sent from the portable hybrid ultrasound diagnosis device and transmits it to the control unit, and the control unit performs a scan conversion process that creates an ultrasound image using the scan data, and then improves the image quality. Post-processing necessary for this purpose is performed, and the control unit also performs a process of decompressing scan data sent from the portable hybrid ultrasound diagnosis apparatus when compressed. In addition, the screen display unit displays the ultrasound image created by the control unit on the screen so that the user can see it, and the menu input unit receives the user's input and transmits it to the control unit, and the control unit directly processes it or uses a data communication unit to perform a portable hybrid ultrasound diagnosis device forward to

In addition, the portable hybrid ultrasound diagnosis apparatus according to the present invention may include a display unit itself. That is, the portable hybrid ultrasound diagnosis apparatus may transmit and display the ultrasound image generated through the communication module to another electronic device, or may be configured to directly display the ultrasound image generated through the communication module.

Embodiments of the present invention have been described above with reference to the drawings. However, this is only described for the purpose of explaining the present invention and is not described to limit or limit the content of the present invention. It will be possible to practice one other embodiment, therefore, the true technical protection scope of the present invention should be defined by the technical matters of the appended claims.

Claims (7)

an ultrasound probe that receives an ultrasound echo signal reflected from the subject after transmitting the ultrasound signal to the subject;
To generate the ultrasound signal, a high voltage pulse is generated and output to the ultrasound probe, ultrasound image data corresponding to the ultrasound echo signal received by the ultrasound probe is generated, and the generated ultrasound image data is transmitted to a display device an ultrasound image generator; and
including a battery for charging and discharging power, and a power supply for supplying power for driving the ultrasound image generator using the power charged in the battery,
The ultrasonic probe is
a first piezoelectric element array for transmitting a linear ultrasound signal from among the ultrasound signals to the subject in response to the high voltage pulse and receiving a linear ultrasound echo signal reflected from the subject;
a second piezoelectric element array for transmitting a convex ultrasound signal from among the ultrasound signals to the subject in response to the high voltage pulse and receiving a convex ultrasound echo signal reflected from the subject;
an array switch unit for switching an operation of any one of the first piezoelectric element array and the second piezoelectric element array in response to an operation control signal transmitted from the ultrasound image generating unit; and
and a multiplexer configured to perform a switching operation to output the high voltage pulse to selected piezoelectric elements among piezoelectric elements constituting the first piezoelectric element array or the second piezoelectric element array,
The operation control signal includes an operation mode selection signal for generating any one of linear scanning data corresponding to the first piezoelectric element array and convex scanning data corresponding to the second piezoelectric element array among the ultrasound image data, ,
The first piezoelectric element array and the second piezoelectric element array,
A portable hybrid ultrasound diagnostic device, characterized in that each faces the front direction and is arranged in parallel with each other in a linear form. delete The method according to claim 1,
The ultrasound image generator,
a pulse generating module for generating an electrical high voltage pulse of any one of the linear ultrasound signal and the convex ultrasound signal according to the operation mode selection signal;
a signal processing module for amplifying the amplitude of any one of the linear ultrasonic echo signal and the convex ultrasonic echo signal and converting it into a digital signal;
a transceiver module for transmitting the high voltage pulse generated by the pulse generating module to the ultrasonic probe, or for receiving the linear ultrasonic echo signal or the convex ultrasonic echo signal from the ultrasonic probe and transmitting it to the signal processing module;
cause the pulse generating module to generate the high voltage pulse corresponding to the ultrasonic probe, and the linear scanning data corresponding to the first piezoelectric element array or the second piezoelectric element according to the digital signal converted by the signal processing module a beamforming module that generates the convex scanning data corresponding to the array;
a processing module controlling the beamforming module to perform beamforming corresponding to the ultrasound probe and transmitting the ultrasound image data received from the beamforming module to the display device; and
and a communication module connected to the display device through a communication network to transmit the linear scanning data or the convex scanning data. 4. The method according to claim 3,
The beamforming module,
According to the operation mode selection signal for generating the linear scanning data, a delay value of the ultrasonic speed or a correction value according to steering is calculated to generate a high voltage pulse corresponding to linear beamforming, characterized in that Portable hybrid ultrasound diagnostic device. 4. The method according to claim 3,
The beamforming module,
and processing to generate a high voltage pulse for virtual convex beamforming according to a distance between the ultrasound probe and the subject according to the operation mode selection signal for generating the convex scanning data. 4. The method according to claim 3,
The processing module,
using a linear scanning conversion algorithm to generate linear ultrasound image data corresponding to the linear scanning data generated by the beamforming module;
The portable hybrid ultrasound diagnosis apparatus of claim 1, wherein the convex ultrasound image data corresponding to the convex scanning data generated by the beamforming module is generated by using a convex scanning conversion algorithm. 7. The method of claim 6,
The processing module,
and generating the operation mode selection signal according to a linear operation mode command or a convex operation mode command generated by the display device and transmitted through the communication module to control the beamforming module.

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