KR101633715B1 - Method and apparatus of performing beamforming - Google Patents

Method and apparatus of performing beamforming Download PDF

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KR101633715B1
KR101633715B1 KR1020160021574A KR20160021574A KR101633715B1 KR 101633715 B1 KR101633715 B1 KR 101633715B1 KR 1020160021574 A KR1020160021574 A KR 1020160021574A KR 20160021574 A KR20160021574 A KR 20160021574A KR 101633715 B1 KR101633715 B1 KR 101633715B1
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임채은
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(주) 성산연구소
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    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A61B8/4461—Features of the scanning mechanism, e.g. for moving the transducer within the housing of the probe
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer

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Abstract

The present invention relates to a method and an apparatus for performing beamforming. According to an embodiment of the present invention, the method for performing beamforming in the apparatus comprises: a step of calculating a first estimation value which is an estimated value from a R_n which is a random value; a step of calculating a calculating value per each sampling from the R_n which is a random value; a step of determining a first R_n as a final R_n, if the calculated value is greater than or equal to the first estimation value; and a step of renewing an estimation value as a second estimation value. The technical purpose of the present invention is to provide a method and an apparatus for performing beamforming, which are capable of efficiently performing beamforming.

Description

[0001] METHOD AND APPARATUS OF PERFORMING BEAMFORMING [0002]

The present invention relates to a method and apparatus for performing beamforming.

The ultrasound diagnostic apparatus transmits an ultrasound signal to an object to be inspected and receives an ultrasound signal reflected from the object. The ultrasound diagnostic apparatus converts the received ultrasound reflection signal into an electrical image signal to show the internal state of the object. The ultrasonic signal is transmitted and received through a probe. The probe includes a transducer for converting an electric signal into an ultrasonic signal and converting the ultrasonic signal reflected from the object into an electric signal. The resolution can be improved by using a probe including a plurality of transducers arranged in various forms.

Korean Patent Publication No. 10-2011-0018187 (published on February 23, 2011) discloses an ultrasonic system having a variable look-up table. The ultrasound system having a variable lookup table includes a data acquisition unit for acquiring ultrasound data, a lookup table generator for generating a variable lookup table according to the position of the obtained ultrasound data, A three-dimensional rendering unit for performing rendering, and a display unit for displaying the performed three-dimensional rendering result.

However, the conventional technique has a problem in that when calculating the distance required for the receive focusing while performing the beam forming, much logic is required in hardware implementation.

SUMMARY OF THE INVENTION The present invention is directed to a method and apparatus for performing beamforming that can efficiently perform beamforming.

A method of performing beamforming in an apparatus for performing beamforming, the method comprising: calculating a first predicted value at an arbitrary R n ; calculating a calculated value in R n, the method comprising or equal to the above calculated value is greater than the first prediction value, determining a second 1R n to a final R n, in the second prediction value comprises a step of updating the first predicted value.

Method for performing beamforming according to one embodiment of the present invention, if the said calculated value is less than the first prediction value, a second step, a step of maintaining the first prediction value to determine the 2R n in the last R n more .

The calculated value is calculated using R n +1 2 = R n 2 + acc_const + 2i * min_step 2 .

And the first predicted value is calculated using R n +1 2 = R n 2 + 2 min_step 2 .

The R n +1 is calculated by adding the min_step to the R n , and the min_step is a unit indicating how many delay addresses are to be calculated for each sampling.

An apparatus for performing beamforming according to an exemplary embodiment of the present invention includes a calculator for calculating a calculated value at an arbitrary Rn for every sampling, a predictor for calculating a first predicted value at the arbitrary Rn, A comparison unit for comparing the calculated value with a first predicted value output from the predictor; a comparison unit for determining a first Rn as a final Rn if the comparison result received by the comparison unit is greater than or equal to the first predicted value; .

The determining unit may determine that if the result of comparison received from the comparison unit the calculated value is less than the first prediction value, a second 2R n R n to end.

And the predictor updates the first predicted value with a second predicted value if the comparison result received by the comparator is greater than or equal to the first predicted value.

The calculated value is calculated using R n +1 2 = R n 2 + acc_const + 2i min_step 2 , and the first predicted value and the second predicted value are calculated using R n +1 2 = R n 2 + 2min_step 2 .

An ultrasonic diagnostic apparatus according to an embodiment of the present invention includes an A / D converter for sampling an analog signal output from a probe at a predetermined sampling rate and converting the analog signal into a digital signal, a digital signal output from the A / And a beamforming unit that receives and performs beamforming, wherein the beamforming unit includes: a calculation unit that calculates a calculation value at an arbitrary R n every sampling; a prediction unit that calculates a first predicted value at the arbitrary R n ; a comparison unit comparing the first predicted value output from the calculation value and the predictor output from the unit, when they have the same comparison result that the calculated value is received from the comparison unit to or greater than the first prediction value, the first 1R n final And R n .

The method and apparatus for performing beamforming according to an embodiment of the present invention have the following effects.

First, the present invention can efficiently perform beam forming.

Second, the present invention can reduce the amount of computation logic performed for beamforming in a hardware implementation of an ultrasonic diagnostic apparatus by performing a square root comparison operation at the time of beamforming.

Third, the present invention can effectively perform the beamforming delay calculation.

FIG. 1 is a schematic view for explaining an ultrasonic diagnostic apparatus including a beam forming unit for performing beam forming according to an embodiment of the present invention.
FIG. 2 is a diagram for explaining a field step for calculating a position of a point at which sampling is performed at the time of beamforming according to an embodiment of the present invention.
3 is a diagram for explaining the principle of a method of performing beamforming according to an embodiment of the present invention.
FIG. 4 is a view for explaining a beam-forming part, which is an apparatus for performing beam forming according to an embodiment of the present invention.
5 is a view for explaining a method of performing beamforming according to an embodiment of the present invention.

BRIEF DESCRIPTION OF THE DRAWINGS The advantages and features of the present invention, and the manner of achieving them, will be apparent from and elucidated with reference to the embodiments described hereinafter in conjunction with the accompanying drawings. However, it is to be understood that the present invention is not limited to the disclosed embodiments, but may be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. It is intended that the disclosure of the present invention be limited only by the terms of the appended claims.

Also, terms used herein are for the purpose of illustrating embodiments and are not intended to limit the invention. In the present specification, the singular form includes plural forms unless otherwise specified in the specification. &Quot; comprises "and / or" comprising "used in the specification do not exclude the presence or addition of components other than the components mentioned. Unless defined otherwise, all terms (including technical and scientific terms) used herein may be used in a sense commonly understood by one of ordinary skill in the art to which this invention belongs.

Rn in the present invention means a sampling distance from any probe element to any target point n. Rn + 1 is the sampling distance from any probe element to any target point n + 1, and Rn-1 is the sampling distance from any probe element to any target point n-1. For example, R1 is the sampling distance from any probe element to any target point 1, and R2 is the sampling distance from any probe element to any target point 2.

The n 1R in the present invention is a value obtained by adding the min_step of s in R n, n is the 2R more values are not the min_step of s in R n.

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

FIG. 1 is a schematic view for explaining an ultrasonic diagnostic apparatus including a beam forming unit for performing beam forming according to an embodiment of the present invention.

1, an ultrasonic diagnostic apparatus includes a probe 10, an A / D converter 20, a beam forming unit 30, a digital receiver 40, a scan conversion unit 50, a display unit 60, (300), a memory (100).

The probe 10 converts an electric signal into an ultrasonic signal, transmits the ultrasonic signal to a target object, receives the ultrasonic signal reflected from the object, and converts the ultrasonic signal into an electric signal (analog signal). The probe 10 includes at least one probe element . The analog signal output from the probe 10 has a center frequency associated with the characteristics of the probe element and the characteristics of the tissue.

The A / D converter 20 samples the analog signal output from the probe 10 at a constant sampling rate (for example, 60 MHz) and converts the sampled signal into a digital signal. In the A / D converter 20, the sampling proceeds at a constant rate irrespective of the magnitude of the center frequency of the analog signal.

When the probe 10 has a plurality of probe elements, the number of the A / D converters 20 corresponding to the number of probe elements transmitting and receiving the ultrasonic waves at the same time may be provided so that the A / D converters 20 may correspond to the respective probe elements one by one .

The beamforming unit 30 forms a reception beam using digital signals output from the A / D converter 20 using a time delay according to a distance difference between the probe element and the object. The resolution can be drastically improved through the beamforming according to the time delay, and the distance of the object changes every sampling, so that the time delay is newly calculated every sampling.

Details of the beamforming unit will be described with reference to FIG.

The digital receiver 40 extracts an echo signal and a frequency component from the beamformed signal in the beamforming unit 30. [ At this time, the beamformed signal in the beamforming unit 30 is an RF (Radio-frequency) signal.

The scan conversion unit 50 performs scan conversion of a demodulated signal appearing in the digital receiver 40 to generate partial image frame data.

The display unit 60 receives the image frame data output from the scan conversion unit 50 and displays the ultrasound image.

The control unit 300 controls the ultrasonic inspection apparatus.

FIG. 2 is a diagram for explaining a field step for calculating a position of a point at which sampling is performed at the time of beamforming according to an embodiment of the present invention.

Referring to FIG. 2, first, in order to explain a field step, a term can be defined in the present invention as shown in Table 1 below.

Terms meaning Variables Used Element location
(element location) Position of any probe element ele_x
ele_z Vector (vector) The elements that make up the image. If n vectors are present, the probe element transmits and receives an ultrasound signal n times. Field start
(field start) Element location where vector begins field_start_x field_start_z Field step
(field step) Angle in which the vector (vector) progresses field_step_x
field_step_z Min Step
(min step) A unit that indicates how many times the Delay address is computed per sampling.
That is, if the delay address is calculated for every n sampling, the microstep has a value of n / 2. For example, if you calculate the delay address for every sampling, the Mins step is 0.5, and if you calculate the delay address every 16 samples, the Mins step is 8. min_step
or
S
(Min_step is represented by s in Equations (7), (6), and (7)

In the present invention, a vector is an element constituting one image. The probe element transmits and receives an ultrasonic signal n times when n vectors are present.

The field represents the region of interest (ROI) of the specimen. That is, the field indicates the position where the vector passes in the traveling direction of the vector. To indicate a field, an increment called a field start point and a field step is required. The field start point refers to the surface to which the probe (or probe element) is touched in vertical flaw detection, and is determined from the position of the probe element. With the field start point as the center, the number of the probe elements determines the beam forming.

The field step proceeds with sampling at any receive beamforming (rx beamforming) and is used to calculate the position of the point to be sampled (target point).

For example, if the vector direction is?, The field step can be expressed by Equation 1 below.

Figure 112016017974302-pat00001

Where field_step_x is the field step in the x direction, field_step_z is the field step in the x direction, and dist_per_sample is the distance per sample. At this time, the unit of the field value is mm.

For example, if the sampling frequency is 40 MHz and the ultrasonic velocity is 5980 m / sec, the dist_per_sample per sample is 0.07475 (5980000 / 40e6 / 2) mm.

Field_step_x is 0, and field_step_z is 0.07475 when the direction of the vector is 0, and field_step_x is 0.07475 * sin (30) = 0.03737 and field_step_z is 0.07475 * cos (30) = 0.06474 when the traveling direction of the vector is 30 degrees. do.

In this way, when a beamforming is implemented by defining a vector and a field, only the angle indicating the direction of the vector is required, so that any type of probe (or probe element) can calculate the field step in the same manner. In particular, since the present invention can calculate multi-beams without the sub-dicing concept of the probe element, it is possible to minimize the occurrence of a gain difference of the multi-beam.

3 is a diagram for explaining the principle of a method of performing beamforming according to an embodiment of the present invention.

Referring to FIG. 3, the total reciprocal distance from the specific probe element 310 to point 1 (x1, z1), point 2 (x2, z2) can be calculated by Equation 2 below.

Figure 112016017974302-pat00002

Here dist1 is the total reciprocal distance from the specific probe element 310 to point 1 (x1, z1) which is the first sampling position and dist2 is the total reciprocal distance from the specific probe element 310 to point 2 (x2, z2 ). ≪ / RTI > Field1 is the distance from the center probe element 300 to the first sampling position point 1 (x1, z1) and field2 is the distance from the center probe element 300 to the second sampling position point 2 (x2, z2) . R1 is the distance from the specific probe element 310 to the first sampling position point 1 (x1, z1), R2 is the distance from the specific probe element 310 to the second sampling position point 2 (x2, z2) .

At this time, R1 is not doubled in dist1, and R2 is not doubled in dist2. The reason why field1 and field2 are used is that in transmission beamforming (tx beamforming) in which an ultrasonic beam (or ultrasonic signal) Because it assumes that the point of the target is pre-focused.

R2, which is a distance required for receiving focusing in the specific probe element 310, can be calculated by Equation (4) through the following Equation (3).

Figure 112016017974302-pat00003

Figure 112016017974302-pat00004

Figure 112016017974302-pat00005

Here, acc_const is a cumulative constant, which can be obtained as shown in Equation (5). Also, i means sampling, where i increases from 0 to 1.

The difference between dist2, which is the total reciprocal distance from the specific probe element 310 to the point 2, and dist1, which is the total reciprocal distance from the specific probe element 310 to the point 1, can be calculated by Equation (6).

Figure 112016017974302-pat00006

Here, min_step can be represented by field2-field1. In Equation (6), the variable min_step is determined according to how many sampling clocks are used for delay calculation. Delay min_step is the number of sampling times divided by 2. At this time, dividing by 2 is because the sampling is calculated based on the round trip time. For example, if you calculate the delay for every sampling, min_step is 0.5, and min_step is 8 if you calculate the delay for every 16 sampling clocks.

Also, since the min_step is a fixed value, the distance difference between dist2 and dist1 can be obtained by (R2-R1).

That is, the difference between the final round trip distance of the point 2 and the point 1 obtained from the equation (6) consists of two items. The first min_step field indicates the tx transmitted to the point where the ultrasound beam is the target, and the second (R2-R1) field indicates the rx received from the target point. Assuming that the focusing is performed at all targets (or target points) at the time of transmitting the ultrasonic beam in the probe element, it has a constant value of min_step, and R2 can be obtained as shown in Equation (3).

In Equation (3), R2 is a distance required for receiving focusing, and a square root is obtained as shown in Equation (3). Square roots can take up a lot of logic in hardware implementations.

In the present invention, i representing sampling is increased from 0 to 1. As such i is the maximum increment of increase for R n R n -1 it is a min_step. For example, as i increases, the maximum increment of R2 for R1 is min_step.

In the present invention, min_step is constantly added to the ultrasonic beam transmission unit tx from the first sampling position to the next sampling position, and the value for rx, which is the ultrasonic beam receiving unit, is equal to or smaller than min_step.

That is, the address sampling distance difference R n -R n for the rx (sampling address) - can be zero or one gatjil min_step of s, and can also be represented by the equation shown in Equation 7 below.

Figure 112016017974302-pat00007

Further, since the value of R n which is finally determined as a value that increases by as much as min_step can be obtained the relationship R n 2.

First, R n and R n +1 can be expressed by Equation (8) below.

Figure 112016017974302-pat00008

Here, Rn + 1 is Rn next sampling address, and s is min_step.

(7) and (8), the following equation (9) is obtained.

Figure 112016017974302-pat00009

Here, ba means that the square difference between each sampling address is expressed by a constant value of 2s 2 . For example, the value of 2s 2 has a value of 0.5 when s, which is min_step, is 0.5, and 128 when s is 8.

Thus, if the min_step is finally determined, the squared difference between the sampling addresses can predict a constant value of 2s 2 .

For example, given a sampling address R 0 at the first target point, the sampling address R 1 at the next target point is determined as (R 0 + s) 2 , the values of R 2 through R n are R n - 1 2 by adding 2 s 2 .

In other words, R 1 is obtained by adding the 2s 2 to R 0, R 2 is obtained by adding the 2s 2 to R 1, R 3 is obtained by adding the 2s 2 to R 2, ... ., R n can be obtained by adding 2s 2 to R n -1 .

4 is a view for explaining a beamforming unit which is an apparatus for performing beamforming according to an embodiment of the present invention.

Referring to FIG. 4, a beamforming unit for performing beamforming according to an embodiment of the present invention includes a calculating unit 410, a predicting unit 420, a comparing unit 430, and a determining unit 440.

The calculation unit 410 calculates a calculation value (for example, R n 2 calculation value) at an arbitrary R n every sampling, and the calculation value of R n 2 can be calculated using the following equation (10).

Figure 112016017974302-pat00010

Equation (10) is a generalization of Equation (3) and is expressed in a form without a square root.

The prediction unit 420 calculates a predicted value (for example, a first predicted value or an estimated R n 2 ) at an arbitrary R n , and the predicted value of R n 2 can be calculated using Equation (11) below.

Figure 112016017974302-pat00011

The comparison unit 430 compares the calculated value (for example, R n 2 calculated value) output from the calculation unit 410 and the predicted value (for example, the first predicted value or R n 2 predicted value) and transmits the comparison result to the predictor 420 and the determiner 440.

Determination unit 440 The comparison result received from the comparing part 430 calculates a value (e. G., R n 2 calculated value) of the predicted value is greater than (e. G., The first predicted value or R n 2 predicted value) or equal to, and outputs the determination to claim 1R n to a final R n.

Alternatively, the determination unit 440 compares a result of the calculation received by the comparison section 430 (e. G., R n 2 measure) a predicted value (for example, the first predicted value or R n 2 predicted value) If less than, and outputs to determine the final 2R n R n.

The prediction unit 420 is a comparison result received from the comparing part 430 calculates a value (e. G., R n 2 calculated value) of the predicted value is greater than (e. G., The first predicted value or R n 2 predicted value) or (For example, the first predicted value or the R n 2 predicted value) is updated with a new predicted value (for example, the second predicted value or the R n + 1 2 predicted value). At this time, a new predicted value (e.g., the second predicted value or the predicted value R n + 1 2 ) may be calculated using Equation (11).

Alternatively, the prediction unit 420 calculates the value comparison result received from the comparing section 430 (e. G., R n 2 measure) a predicted value (for example, the first predicted value or R n 2 predicted value) The predicted value (for example, the first predicted value or the R n 2 predicted value) is not updated with the new predicted value (e.g., the second predicted value or the R n + 1 2 predicted value).

5 is a view for explaining a method of performing beamforming according to an embodiment of the present invention.

Referring to FIG. 5, the apparatus for performing beamforming calculates a first predicted value, which is a predicted value, at an arbitrary R n (S510). For example, the predicted value at an arbitrary R n can be calculated by the above Equation (11) as a predicted value of R n 2 .

The apparatus for performing beamforming calculates a calculation value at an arbitrary R n every sampling (S520). For example, the calculation value at an arbitrary R n can be calculated as the calculation value of R n 2 by the above Equation (10).

The apparatus for performing beamforming checks whether the calculated value is greater than or equal to the first predicted value (S530).

A device that performs beamforming is computed value is equal to or greater than the first prediction value, and determines the second final 1R n R n (S540).

The beamforming apparatus updates the first predicted value with the second predicted value (S550). For example, the second predicted value may be a predicted value of R n + 1 2 , and can be obtained using Equation (11).

The apparatus for performing the beam forming is if the calculated value is less than the first prediction value, determining a second 2R n to a final R n (S560).

The apparatus for performing beamforming maintains a first predicted value (S570). That is, the apparatus for performing beamforming maintains the first predicted value as a predicted value.

The method according to an embodiment of the present invention may be implemented in the form of a program command that can be executed through various computer means and recorded in a computer-readable recording medium. The computer-readable recording medium may include program instructions, data files, data structures, and the like, alone or in combination. The program (program instructions) to be recorded on the recording medium may be those specially designed and configured for the present invention or may be those known to those skilled in the computer software. Examples of the computer-readable recording medium include magnetic media such as a hard disk, a floppy disk and a magnetic tape, optical media such as a CDROM and a DVD, magneto-optical media such as a floppy disk, Hardware devices that are specifically configured to store and execute program instructions such as magneto-optical media, ROM, RAM, flash memory, and the like. Examples of program instructions include machine language code such as those produced by a compiler, as well as high-level language code that can be executed by a computer using an interpreter or the like. The hardware devices described above may be configured to operate as one or more software modules to perform the operations of the present invention, and vice versa.

While the present invention has been particularly shown and described with reference to exemplary embodiments thereof, it is to be understood that the invention is not limited to the disclosed exemplary embodiments, but, on the contrary, It will be appreciated that one embodiment is possible. Accordingly, the true scope of the present invention should be determined by the technical idea of the claims.

10: Probe
20: A / D converter
30: beam forming section
40: Digital receiver
50: scan conversion section
60:
70:
300: center probe element
310: Specific probe element
410:
420:
430:
440:

Claims (10)

A method for performing beamforming in an apparatus that performs beamforming,
Calculating a first predicted value that is a predicted value from an arbitrary R n ,
Calculating a computation value at said arbitrary R n for each sampling,
The method comprising the calculated value is equal to or greater than the first prediction value, determining a first end-R 1R as n n,
And updating the first predicted value to a second predicted value,
Where R n is the sampling distance from any probe element to any target point n,
And wherein n is the sum of the 1R min_step to the arbitrary value, R n,
Wherein the min_step is a unit indicating how many delay addresses are to be calculated for each sampling. The method according to claim 1,
Further comprising: if the calculated value is less than the first prediction value, determining a second 2R n R n to the end,
Further comprising maintaining the first predicted value,
2R wherein n is a method of performing beam-forming, characterized in that the value is not more min_step to the arbitrary R n. 3. The method of claim 2,
The calculated value is calculated using R n + 1 2 = R n 2 + acc_const + 2i * min_step 2 ,
Wherein the acc_const is a cumulative constant and the i is a unit for sampling. 3. The method of claim 2,
Wherein the first predicted value is calculated using R n +1 2 = R n 2 + 2 min_step 2 . 5. The method of claim 4,
Rn + 1 = Rn + min_step. ≪ / RTI > A calculation unit for calculating a calculation value at an arbitrary R n every sampling,
A predictor for calculating a first predicted value, which is a predicted value, from the arbitrary R n ;
A comparing unit comparing the calculated value output from the calculating unit with a first predicted value output from the predicting unit,
The compared result received from the comparator equal to the calculated value is equal to or greater than the first prediction value, comprising: determination unit which determines the first finally 1R n R n,
Where R n is the sampling distance from any probe element to any target point n,
And wherein n is the sum of the 1R min_step to the arbitrary value, R n,
Wherein the min_step is a unit indicating how many delay addresses are to be calculated for each sampling. The method according to claim 6,
The determination section determines, but if the result of comparison received from the comparison unit the calculated value is less than the first prediction value, a second 2R n R n to the final,
And the second R n is a value that does not add the min_step to the arbitrary R n . 8. The method of claim 7,
Wherein the predicting unit updates the first predicted value with a second predicted value when the comparison result received by the comparison unit is equal to or greater than the first predicted value. 9. The method of claim 8,
The calculated value is calculated using R n + 1 2 = R n 2 + acc_const + 2i * min_step 2 ,
The first predicted value and the second predicted value are calculated using R n + 1 2 = R n 2 + 2 min -
Wherein the acc_const is a cumulative constant and the i is a unit for sampling. An A / D converter that samples an analog signal output from the probe at a predetermined sampling rate and converts the sampled signal into a digital signal,
And a beamforming unit for receiving the digital signal output from the A / D converter and performing beamforming,
The beam forming section
A calculation unit for calculating a calculation value at an arbitrary R n every sampling,
A predictor for calculating a first predicted value, which is a predicted value, from the arbitrary R n ;
A comparing unit comparing the calculated value output from the calculating unit with a first predicted value output from the predicting unit,
The compared result received from the comparator equal to the calculated value is equal to or greater than the first prediction value, comprising: determination unit which determines the first finally 1R n R n,
Where R n is the sampling distance from any probe element to any target point n,
And wherein n is the sum of the 1R min_step to the arbitrary value, R n,
Wherein the min_step is a unit indicating how many delay addresses are to be calculated for each sampling.
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Citations (4)

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Publication number Priority date Publication date Assignee Title
JP2000333951A (en) * 1999-05-26 2000-12-05 Ge Yokogawa Medical Systems Ltd Ultrasonic image pickup device
JP2001202498A (en) * 2000-01-19 2001-07-27 Olympus Optical Co Ltd Method and device for recomposing ultrasonic three- dimensional picture
KR20070113084A (en) * 2006-05-23 2007-11-28 주식회사 메디슨 Ultrasound diagnostic system and method for forming multiple receiving scan lines
KR20080057499A (en) * 2006-12-20 2008-06-25 재단법인 포항산업과학연구원 Apparatus and method for processing ultrasonic signal

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000333951A (en) * 1999-05-26 2000-12-05 Ge Yokogawa Medical Systems Ltd Ultrasonic image pickup device
JP2001202498A (en) * 2000-01-19 2001-07-27 Olympus Optical Co Ltd Method and device for recomposing ultrasonic three- dimensional picture
KR20070113084A (en) * 2006-05-23 2007-11-28 주식회사 메디슨 Ultrasound diagnostic system and method for forming multiple receiving scan lines
KR20080057499A (en) * 2006-12-20 2008-06-25 재단법인 포항산업과학연구원 Apparatus and method for processing ultrasonic signal

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