CN1287740C - Method of detecting moving velocity of tissue or blood and ultrasonic diagnosing apparatus - Google Patents
Method of detecting moving velocity of tissue or blood and ultrasonic diagnosing apparatus Download PDFInfo
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- CN1287740C CN1287740C CN 95116348 CN95116348A CN1287740C CN 1287740 C CN1287740 C CN 1287740C CN 95116348 CN95116348 CN 95116348 CN 95116348 A CN95116348 A CN 95116348A CN 1287740 C CN1287740 C CN 1287740C
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Abstract
A plurality of ultrasonic pulses are transferred to a human body by an ultrasonic probe and an ultrasonic echo signal is received from the human body. The ultrasonic echo signal is autocorrelated by an autocorrelator to generate a real part component and a virtual part component and a real part component corrector adds an offset value to the real part component so as to generate a new real part component. A speed detector detects the movement velocity of tissues or blood according to the new real part component and the virtual part component.
Description
Technical field
The present invention relates to detect the method for the movement velocity (being blood flow rate) of the movement velocity relevant speed of motion of tissues such as heart wall (promptly with) of tissue or blood, can prevent that with this method measured movement velocity is bigger than actual speed, the invention still further relates to a kind of diagnostic ultrasound equipment that adopts this method.
Background technology
Fig. 4 is the block diagram of an embodiment of the explanation conventional ultrasonic wave diagnostic equipment.
The reference signal of quadrature detector 4 usefulness ultrasonic echo signal times to be produced from reference signal generator 3 is so that export an in-phase component I and a quadrature component Q.
Each A/ D changer 5 and 6 is finished the A/D conversion of in-phase component I and quadrature component Q.
When from body measurements histokinesis speed, switch 7a and 8b are transformed into the side shown in solid line among Fig. 4 respectively, so that the in-phase component I and the quadrature component Q that have passed through after the A/D conversion need not just be imported into an autocorrelator 9 by MTI (portable target indication) wave filter 7 and 8.On the other hand, when carrying out blood flowing speed when measuring, switch 7a and 8b are transformed into a side shown in dotted lines in Figure 4 respectively, so that through in the in-phase component I of A/D conversion and quadrature component Q each self- corresponding mti filter 7 and 8 that is imported into them.
The multiplier 9C of autocorrelator 9 will be corresponding to the i in a plurality of ultrasonic pulses (=2,3,) individual pulse quadrature component Qi with multiply each other corresponding to the quadrature component Qi-1 of (i-1) individual pulse, (wherein Qi-1 is by the delayer 9a of free delay action output), and output result of product QiQi-1.Similarly, multiplier 9d multiplies each other quadrature component Qi-1 and in-phase component Ii, exports the result of product of IiQi-1 then.And similarly, multiplier 9e multiplies each other quadrature component Qi and the in-phase component Ii-1 that is produced by the delayer 9b that has time delay, exports the result of product of QiIi-1 then.In addition, multiplier 9g multiplies each other in-phase component Ii and in-phase component Ii-1, exports the result of product of IiIi-1 then.
Adder 9h is the output IiIi-1 addition of the output QiQi-1 of multiplier 9c and multiplier 9g, and (=IiIi-1+QiQi-1) result of product is delivered to average calculating operation device 9P being equivalent to real component Rei.9P couple of real component Rei relevant with all i of average calculating operation device averages, and then resulting average real components R e exported to speed detector 12.
On the other hand, subtractor 9K deducts the output IiQi-1 of multiplier 9d from the output QiIi-1 of multiplier 9e, and (=QiIi-1-IiQi-1) the result that subtracts each other exports an average calculating operation device 9q to corresponding to imaginary part component Imi.Average calculating operation device 9q carries out average operation to the imaginary part component Imi with respect to all i, and the average imaginary part component Im that obtains is exported to speed detector 12.
Speed detector 12 is calculated as follows out speed V:
V＝K·tan-1(Im/Re)
(K=C/ (4 π foT) here
C: hyperacoustic speed in the human body
Fo: transmit frequency of ultrasonic
T: pulse recurrence interval T=2d/c
D: the diagnosis distance)
Speed V represents to organize or the movement velocity of blood, and it is imported among the DSC13.
The ultrasonic echo signal that is received by ultrasound probe 1 inputs to a B schema processor 15 by the transmission-receptor 2 that separates with described ultrasound echo signal.
B schema processor 15 produces B mode image data according to the ultrasound wave echo signal, and it is inputed to DSC13.
DSC13 is according to above-mentioned speed V and B ideograph image data, stacking up by the movement velocity of tissue or blood being carried out image and B pattern image that coloud coding obtains, obtains a width of cloth chromatic image, and the generation data relevant with this chromatic image.
CRT14 demonstrates chromatic image according to color image data on screen.
Fig. 5 is used to describe real component Re, imaginary part component Im, a sketch that concerns between speed V and the power P.
Vector on plural coordinate (Re, angle tan-1 Im) (Im/Re) expression speed V, amplitude={ Re
2+ Im
2}
1/2Represent power P.In other words, speed does not depend on power P.
Therefore, speed Vb that is measured by diagnostic ultrasound equipment 500 and the relativeness between the power P are as shown in Figure 6.The speed Vb that records depends on power P, and when power P reduced, Vb became a more irregular value that differs widely with actual speed V.
It is believed that, this is because added further specifies vector (Re by noise or the similar non-specifies vector Na and the Ni that are produced of disturbing, Im) in, these specifies vector are uncertain, it is shown in the round Nc among Fig. 7, when power P was low, determined speed Vb just became a more irregular value, and the degree of its scrambling reaches several times of actual speed V.
Therefore, just such problem occurs, as tested speed Vb during much larger than actual speed V, tissue or blood flow seem just undesired.Another problem is owing to give the image colouring without meaning, an inappropriate color flow cardon can occur and resemble.
Summary of the invention
For this reason, an object of the present invention is to provide the method that detects tissue or blood motion speed, when power P reduced, it can prevent that tested speed is bigger than the value of actual speed.
According to a first aspect of the invention, the method that is provided may further comprise the steps: a series of a plurality of ultrasonic pulses are transferred to inside of human body from a ultrasound probe, reception is by the ultrasonic echo signal that returns in the human body, this ultrasonic echo signal is carried out auto-correlation processing, obtain a real component and an imaginary part component, the movement velocity of coming human body tissue or blood according to described real component and imaginary part component, wherein said method also comprises step: after adding a bias in the described real component, detect the movement velocity of tissue or blood, so that when low-power, the movement velocity that is detected is no more than actual movement velocity.
According to a second aspect of the invention, the diagnostic ultrasound equipment that is provided comprises: a ultrasound probe is used for a plurality of ultrasonic pulses are sent to inside of human body, and receives the ultrasonic echo signal in human body; The self correlation device is used for received ultrasonic echo signal is carried out auto-correlation processing; The movement velocity checkout gear is used for detecting movement velocity according to a real component and an imaginary part component from described self correlation device output; Wherein said diagnostic ultrasound equipment also comprises: be arranged on the real component correcting unit between described self correlation device and the described movement velocity checkout gear, be used for a bias is added described real component, so that when low-power, the movement velocity that is detected is no more than actual movement velocity.
In described tissue or blood motion speed detection method and diagnostic ultrasound equipment, by ultrasound probe a plurality of ultrasonic pulses are sent in the human body, and in human body, received the ultrasonic echo signal.The ultrasonic echo signal is carried out auto-correlation processing, so that produce real component and imaginary part component.Then, a bias is added in the real component so that produce a new real component.Then, determine the movement velocity of tissue or blood according to this new real component and described imaginary part component.
Primary real component and imaginary part component represent with Re and Im that respectively bias is represented with r, can draw following inequality like this:
tan-1{Im/(Re+r)}＜tan-1(Im/Re)
If bias r is configured to a desired value, just can prevent that speed V arrival is much larger than a value of actual speed when power P reduces.
When power P was big, it is more much bigger than bias r that original real component Re just becomes, and at this moment can draw following inequality:
tan-1{Im/Re+r)}＝tan-1(Im/Re)
Here can ignore the influence of additional bias r to real component.
Therefore, according to this tissue or blood motion speed detecting method and this diagnostic ultrasound equipment, when power P is lowered, can prevent that determined speed from becoming greater than actual speed.So can prevent to organize mistakenly or blood flow is judged as unusually.In addition, can also prevent owing to inappropriate color flow cardon occurring for without meaning the image colouring.
Description of drawings
Above-mentioned and other purposes of the present invention, feature and advantage will find out obviously that in conjunction with each accompanying drawing most preferred embodiment wherein of the present invention can be described by example from following description and attached each claim.
Fig. 1 is the block diagram according to an embodiment of diagnostic ultrasound equipment of the present invention;
Fig. 2 is used to describe original real component Re, original imaginary part component Im, true velocity V, power P, a sketch of corresponding relation between new real component Re ' and the determined speed V ';
Fig. 3 is a sketch that is used to describe relation between power P and the determined speed V ';
Fig. 4 is the block chart of an example of the explanation conventional ultrasonic wave diagnostic equipment;
Fig. 5 is used to describe real part molecular weight Re, imaginary part component Im, a sketch that concerns between true velocity V and the power P;
Fig. 6 is used to describe a sketch that concerns between power P and the determined speed Vb;
Fig. 7 is a figure who is used to describe the race conditio of determined speed.
The specific embodiment
The present invention will use most preferred embodiment to do and describe in further detail in the back with reference to several accompanying drawings.The present invention is not subjected to the restriction that above-mentioned enforcement is fallen.
Fig. 1 is the block diagram according to an embodiment of diagnostic ultrasound equipment of the present invention.
The reference signal of quadrature detector 4 usefulness ultrasonic echo signal times to be produced by reference signal generator 3 so just can be exported an in-phase component I and a quadrature component Q.
Each A/D changer 5 and the 6 couples of in-phase component I and quadrature component Q carry out the A/D conversion.
When from the movement velocity of body measurements tissue, switch 7a and 8b are transformed into a side shown in the solid line among Fig. 1 respectively, make the in-phase component I and the quadrature component Q that have passed through the A/D conversion just to output to an autocorrelator 9 by mti filter 7 and 8.On the other hand, when measuring blood flowing speed, switch 7a and 8b are transformed into a side as shown in phantom in Figure 1 respectively, make the in-phase component I that passed through the A/D conversion and quadrature component Q each self-corresponding MTI filtering 7 and 8 that is imported into them.
A multiplier 9C of autocorrelator 9 corresponding to the i in a plurality of ultrasonic pulses (=2,3,) individual pulse quadrature component Qi with multiply each other (Qi-1 be from the delayer 9a output that has time delay) corresponding to the quadrature component Qi-1 of (i-1) individual pulse, and output result of product QiQi-1.Similarly, multiplier 9d multiplies each other in-phase component Ii and quadrature component Qi-1, and output result of product IiQi-1.And similarly, multiplier 9e multiplies each other quadrature component Qi and the in-phase component Ii-1 that produces from the delayer 9b that has time delay, exports result of product QiIi-1 then.In addition, multiplier 9g multiplies each other in-phase component Ii and in-phase component Ii-1, output result of product IiIi-1.
Adder 9h is the output IiIi-1 addition of the output QiQi-1 of multiplier 9c and multiplier 9g, and the result of product that is equivalent to a real component Rei=(IiIi-1+QiQi-1) is delivered to an average calculating operation device 9p.Average calculating operation device 9p averages operation to the real component Rei that relates to all i, and resulting average real components R e is defeated by real component corrector 10.
On the other hand, subtractor 9K deducts the output IiQi-1 of multiplier 9d from the output QiIi-1 of multiplier 9e, and (=QiIi-1-IiQi-1) the result that subtracts each other exports to an average calculating operation device 9q being equivalent to imaginary part component Imi.Average calculating operation device 9q averages computing to the imaginary part component Imi that relates to all i, and resulting average imaginary part component Im is exported to speed detector 12.
Real component corrector 10 a bias r who comes from bias feeder 11 join among the real component Re with produce a new real component Re ' (=Re+r), it is output to speed detector 12.
Now, when the movement velocity to tissue detected, when no signal, bias r was preferably fixed to several times that are equivalent to real component Re big, to eliminate the noise corresponding to non-command speed component.On the other hand, when the flow velocity to blood detected, biasing r was preferably fixed to corresponding to several times big of any movement velocity value of 2cm/s in the 3cm/s scope, to eliminate or to control histokinesis's component of the non-command speed component of representative.
Speed detector 12 calculates speed V ' according to following formula.In addition, speed detector 12 is exported to a DSC13 to result of calculation.
V′＝K·tan-1(Im/Re′)
(K=C/ (4 π foT) here
C: hyperacoustic speed in the human body
Fo: transmit frequency of ultrasonic
T: pulse recurrence interval T=2d/c
D: the diagnosis distance)
The ultrasonic echo signal that is received by ultrasound probe 1 inputs to a B schema processor 15 by transmission-receptor 2 of separating with described ultrasonic echo signal.
B schema processor 15 produces B ideograph image data according to the ultrasound wave echo signal, and it is inputed to DSC13.
DSC13 is according to above-mentioned speed V ' and B ideograph image data, stacking up by the movement velocity of tissue or blood being carried out image and B pattern image that coloud coding obtains, obtains a width of cloth chromatic image, and the generation data relevant with this chromatic image.
CRT14 demonstrates on screen according to color image data and is with chromatic image.
Fig. 2 is used to describe the original imaginary part component of original real component Re Im, actual speed V, power P, a sketch of mutual relation between new real component Re ' and the tested speed V '.
Vector (Re, angle tan-1 Im) (Im/Re) represents actual speed V, and length={ Re2+Im2} represents power P.Vector (Re ', angle tan-1 Im) (Im/Re ') represent determined speed '.
Can know from Fig. 2, when non-specifies vector Na and Ni added original vector (Re, Im) in the time, in case power P reduces, determined speed Vbmin reaches several times of actual speed V to Vbmax.But, even non-specifies vector Na and Ni be added to new vector (Re ', Im) in the time, tested speed Vb ' min still can fall into than in the also low velocity interval of actual speed V to Vb ' max.
Therefore, Fig. 3 has represented the relation between speed V ' and the power P.Speed V ' is restricted, and its setting value can be not bigger than actual speed V.So also can prevent to see inappropriate phenomenon of tissue or blood flow.In addition, also can prevent from inappropriate color flow cardon to occur for the image colouring owing to being not intended to the free burial ground for the destitute.
Entirely described the present invention now, many for a person skilled in the art variations and distortion will be conspicuous, and all not break away from the aforesaid spirit and scope of the present invention.
Claims (2)
1. method of measuring the movement velocity of tissue or blood, may further comprise the steps: a series of a plurality of ultrasonic pulses are transferred to inside of human body from a ultrasound probe, reception is by the ultrasonic echo signal that returns in the human body, this ultrasonic echo signal is carried out auto-correlation processing, obtain a real component and an imaginary part component, the movement velocity of coming human body tissue or blood according to described real component and imaginary part component, wherein said method also comprises step: after adding a bias in the described real component, detect the movement velocity of tissue or blood, so that when low-power, the movement velocity that is detected is no more than actual movement velocity.
2. diagnostic ultrasound equipment comprises:
A ultrasound probe is used for a plurality of ultrasonic pulses are sent to inside of human body, and receives the ultrasonic echo signal in human body;
The self correlation device is used for received ultrasonic echo signal is carried out auto-correlation processing;
The movement velocity checkout gear is used for detecting movement velocity according to a real component and an imaginary part component from described self correlation device output; Wherein said diagnostic ultrasound equipment also comprises:
Be arranged on the real component correcting unit between described self correlation device and the described movement velocity checkout gear, be used for a bias is added described real component, so that when low-power, the movement velocity that is detected is no more than actual movement velocity.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 95116348 CN1287740C (en) | 1995-08-08 | 1995-08-08 | Method of detecting moving velocity of tissue or blood and ultrasonic diagnosing apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 95116348 CN1287740C (en) | 1995-08-08 | 1995-08-08 | Method of detecting moving velocity of tissue or blood and ultrasonic diagnosing apparatus |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1142348A CN1142348A (en) | 1997-02-12 |
| CN1287740C true CN1287740C (en) | 2006-12-06 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 95116348 Expired - Fee Related CN1287740C (en) | 1995-08-08 | 1995-08-08 | Method of detecting moving velocity of tissue or blood and ultrasonic diagnosing apparatus |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| US7946991B2 (en) * | 2003-10-17 | 2011-05-24 | Panasonic Corporation | Ultrasonic doppler blood flow measuring device |
| CN100469320C (en) | 2005-09-29 | 2009-03-18 | 深圳迈瑞生物医疗电子股份有限公司 | Method for eliminating speed abnormal point in color blood-stream image |
| CN104458916B (en) * | 2013-09-16 | 2019-05-28 | 林德博公司 | For measuring the system or method of liquid or gas stream |
| CN109640827B (en) * | 2016-03-23 | 2022-04-29 | 皇家飞利浦有限公司 | Method and apparatus for improving the measurement of blood flow rate |
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1995
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| CN1142348A (en) | 1997-02-12 |
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