CN105476665B - A kind of blood flow velocity measurement and blood flow flow-measuring method based on ultrasound - Google Patents
A kind of blood flow velocity measurement and blood flow flow-measuring method based on ultrasound Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
- A61B8/5223—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for extracting a diagnostic or physiological parameter from medical diagnostic data
Abstract
The present invention relates to ultrasonic imaging field, in particular to a kind of blood flow velocity measurement method and blood flow flow-measuring method based on ultrasound.Blood flow velocity measurement method provided by the invention carries out sub-sampling division by I/Q signal of N number of sub-sampling window comprising the full depth bounds of blood vessel to acquisition, it avoids in traditional D mode imaging, doctor need to constantly move sub-sampling window, and be only capable of being located at the defect that the position in sub-sampling window is detected to blood vessel；The blood distribution information of each depth location of blood vessel can be provided for user；Simultaneously, blood flow flow-measuring method provided by the invention is due to simultaneously to progress child window sampling in the full depth bounds of blood vessel, obtain the blood flow information of each position in the full depth bounds of blood vessel, and then the blood flow flow and blood flow flow jitter index more accurate according to the blood speed information acquisition in each depth bounds of blood vessel.
Description
Technical field
The present invention relates to ultrasonic measurement field, in particular to a kind of blood flow velocity measurement method and blood flow stream based on ultrasound
Measuring method.
Background technique
In traditional ultrasonic Blood diagnosis, doctor mostly uses ultrasonic B-mode imaging results or D mode that (also known as pulse is imaged
The imaging of wave Doppler frequency spectrum) result diagnoses blood flow disease, but since many blood flow diseases are that B-mode imaging can not be seen
(such as vascular sclerosis and vascular wall early stage disease) surveyed, therefore D mode is imaged and is more and more widely used；But, by
In technical restriction, existing D mode imaging only includes 1 sub- sampling window mostly, while the range that the sub-sampling window includes
Very small (under D mode, can only observe the blood flowing speed information in sub-sampling window), doctor need constantly to move the son and adopt
Sample window observes the blood flow information of blood vessel different depth, different location, and it is low that this undoubtedly results in detection efficiency.
Meanwhile when measuring to blood flow flow, 1 sub- sampling window is used only in existing D mode imaging, is obtained
Blood flow velocity is the average speed of entire blood vessel, therefore its measurement result accuracy is very poor.
Summary of the invention
It is an object of the invention to overcome in existing D mode imaging (Pulsed-Wave Doppler spectral imaging) technology, due to
Technical restriction, the low problem of detection efficiency caused by an only sub- sampling window provide a kind of comprising the full depth letter of blood vessel
The blood flow information imaging method of more sub-sampling windows of breath.
Herein, vessel depth refer to tested vessel cross-sections diametrically any point to a selected end of the diameter away from
From value.
In order to achieve the above-mentioned object of the invention, the present invention provides following technical schemes:
A kind of blood flow velocity measurement method based on ultrasound,
It is tested endovascular feedback radiofrequency signal certainly comprising receiving acquisition, and by the radiofrequency signal after Hilbert transform
The step of obtaining discrete I/Q signal；
Also comprise the following steps:
Discrete I/Q signal is subjected to sub-sampling division by N number of sub-sampling door, N number of sub-sampling door includes all deep of blood vessel
Spend range；N number of sub-sampling door can be non-cross or be slightly intersected；N is 2 or more natural numbers；
I/Q signal sequence in each sub-sampling door is subjected to compound time-domain signal, wall filter filtering, frequency domain conversion,
Generate frequency-region signal；
It is imaged after calculating amplitude spectrum in the frequency-region signal obtained.
Further, the number N of sub-sampling door is determined by vessel depth and the impulse wave wavelength, i.e.,Due to sound physical properties constraint, the velocity estimation in an impulse wave wavelength is can not be again
Point, so achieved most accurate velocity estimation is an impulse wave wavelength at present, so a sub- sampling gate, is
The length of the length of at least one impulse wave wavelength or multiple impulse wave wavelength.
Preferably, the number of sub-sampling door takes qualified maximum even number, from the foregoing, it will be observed that the optimum length of sub-sampling door
It should be the length of an impulse wave wavelength, but show and calculate for the ease of subsequent image, it is preferably that vessel depth is symmetrical
It divides, i.e., respectively has N/2 sub- sampling gates from blood vessel center to two sides.
Further, the size (i.e. sample variance signal number in a pulse wavelength) of sub-sampling door is by formulaIt obtains, wherein m is the pulse signal number for including in the impulse wave for detection, is 1 or more natural
Number, FsIt is sample frequency, FcIt is the centre frequency of pulse signal, the sampled point for each pulse signal, in each wavelength
Number=sample frequency/(2* signal center frequency)；Therefore for the impulse wave comprising m pulse signal, group sampling gate
Length when being signal wavelength, the discrete sampling points for including in each sub-sampling door areIt is a, it, can be under some embodiments
Pass through formulaDetermine the number of sub-sampling door N,Wherein, NnumFor collected radiofrequency signal
Length, i.e., the number of collected discrete signal from blood vessel；In Fs、FcAnd under the premise of tested blood vessel diameter is identical,
Further, the time-domain signal is compound uses formula sk(i)=∑ s (i, k) is carried out, and wherein i indicates IQ letter
Discrete serial number number in time, k is the serial number of sub-sampling door；S (i, k) indicates that the IQ at i moment in k-th of sub-sampling door is original
Signal, sk(i) signal after time-domain meets operation is indicated.
Further, I/Q signal is converted into frequency-region signal using formulaIt carries out；
Wherein, W indicates the window size of Short-time Window Fourier transformation,Frequency-region signal after indicating conversion.
Further, in the step of obtaining amplitude spectrum imaging, the amplitude spectrum passes through formulaIt obtains.
Further, after calculating amplitude spectrum in the frequency-region signal obtained, further include the steps that improving spectrum contrast；
It realizes formula are as follows: P (t, ω)=∑ P by the way that amplitude spectrum to be done to composition operation realization on frequency domaink(t,ω).By
After composition operation on frequency domain, the amplitude spectrum contrast of intravascular each depth can be made to be obviously improved, it can also be effectively
Inhibition noise, improve frequency spectrum signal-to-noise ratio, effectively enhance frequency spectrum detail resolution, truly both inhibited noise and also promoted frequency
Compose detail resolution.
Preferably, after the radiofrequency signal is converted to I/Q signal, further include the steps that, by low-pass filtering, low-pass filtering is used
In filtering out DC component and idling frequency in signal.
It preferably, further include to picture smooth treatment, compression after calculating amplitude spectrum imaging in the frequency-region signal obtained
The step of processing.
For the present invention in order to overcome existing D mode imaging that 1 sub- sampling window is used only, the blood flow velocity obtained is whole
The average speed of a blood vessel, therefore the problem that its measurement result accuracy is very poor provide a kind of comprising the full depth information of blood vessel
The blood flow flow-measuring method of more sub-sampling windows includes blood flow velocity measurement method as described above；Further include:
T is calculated according to amplitude spectrumjBlood flow velocity distributed intelligence V (k, the t at momentj) the step of；
By blood flow velocity distributed intelligence V (k, tj) integrate the step of obtaining blood flow flow；
Further, any t is calculated according to amplitude spectrumjBlood flow velocity distributed intelligence V (k, the t at momentj) using following public
Formula:Wherein, ViIndicate tjK-th of sub-sampling door amplitude spectrum P of momentk(T, ω) is corresponding
Blood speed；
In the step of blood flow velocity distributed intelligence V (k, T) integral is obtained blood flow flow, blood flow flow:Discrete representation isWherein, r is sub-sampling
Gate-width degree, R are tested vessel radius.
Further, further include the steps that carrying out angle modification to blood flow flow；Revised blood flow flowWherein s indicates the heart contraction moment in single heartbeat period, and d was indicated in the heartbeat period
Diastolic time, α indicates the angle between vascular wall and sub-sampling door.
Further, further include the steps that calculating blood flow flow jitter index, blood flow flow jitter indexWherein NhFor cardiac cycle number, xiIndicate that blood flow flow when single cardiac cycle number, u are
Blood flow flow average value during entire measurement.
Compared with prior art, beneficial effects of the present invention: with traditional D mode imaging method (Pulsed-Wave Doppler frequency
Spectrum imaging method) it compares, blood flow velocity measurement method provided by the invention passes through N number of sub-sampling comprising the full depth bounds of blood vessel
Window carries out sub-sampling division to the I/Q signal of acquisition, and further by carrying out the I/Q signal in each sub-sampling window
Time-domain is compound, frequency domain conversion, frequency domain are compound etc. operates to obtain blood flowing speed information in the full depth bounds of blood vessel everywhere, avoids
In the imaging of traditional D mode, doctor need to constantly move sub-sampling window, and be only capable of position blood vessel being located in sub-sampling window into
The defect of row detection；Due to imaging method provided by the invention, while to child window sampling is carried out in the full depth bounds of blood vessel, obtain
The blood flow information of each position in the full depth bounds of blood vessel is taken, therefore, user can choose while watch the blood flow of entire blood vessel
Information distribution, also can choose the blood flow information of a certain depth any time or any time period in blood vessel, to reduce
Detection time improves detection efficiency, simplifies detection difficulty.
Meanwhile blood flow flow-measuring method provided by the invention is due to simultaneously to carrying out child window in the full depth bounds of blood vessel
Sampling obtains the blood flow information of each position in the full depth bounds of blood vessel, and then according to the blood speed in each depth bounds of blood vessel
The more accurate blood flow flow of information acquisition and blood flow flow jitter index.
Detailed description of the invention:
Fig. 1 is the flow chart of blood flow velocity measurement method specific embodiment of the present invention.
Fig. 2 a is the image display example block diagram in the specific embodiment of the invention.
Fig. 2 b is that the image in the specific embodiment of the invention shows example.
Fig. 3 a is the three-dimensional model diagram of each deep blood flow speed of blood vessel obtained using the image method of the invention.
Fig. 3 b is associated with signal with each area image in Fig. 2 a, Fig. 2 b for three-dimensional model diagram in Fig. 3 a.
Another image display example block diagram in Fig. 4 a specific embodiment of the invention.
Another image image in Fig. 4 b specific embodiment of the invention shows example.
Fig. 5 is blood flow flow-measuring method flow chart provided by the invention.
Fig. 6 is the blood flow flow illustrated example corresponding with time of measuring being calculated.
Fig. 7 is the blood flow flow illustrated example corresponding with the heartbeat period being calculated.
Specific embodiment
With reference to the accompanying drawing and specific embodiment the present invention is described in further detail.But this should not be interpreted as to this
The range for inventing above-mentioned theme is only limitted to embodiment below, all to belong to the present invention based on the technology that the content of present invention is realized
Range.
Embodiment 1: as shown in Figure 1, the present embodiment provides a kind of blood flow velocity measurement methods based on ultrasound；Comprising as follows
Step:
S100: it receives acquisition and is tested endovascular feedback radiofrequency signal certainly, and by the radiofrequency signal through Hilbert transform
After the step of obtaining discrete I/Q signal；The feedback radiofrequency signal is the pulsed ultrasonic wave emitted according to predetermined pulse repetition rate
Feedback radiofrequency signal after being detected to blood vessel.
In this step, the following formula of process for obtaining discrete I/Q signal by Hilbert transform is expressed:
Wherein, FcIt is the centre frequency of each pulse signal in impulse wave, FsIt is sample frequency, NnumBelieve for the radio frequency of acquisition
Number length, i.e., the number of collected discrete signal from blood vessel；Such as, when sample frequency is that (each second samples 20M to 20MHz
A sampled point) when, the rate of sound wave pulse wave is 1540m/s (spread speed of sound in human body), then in sampling frequency
It is per cm to have 260 sampled points under rate, it is assumed that arteria carotis width is 0.8cm, then at this point, the length of the radiofrequency signal of acquisition
Spend Nnum=0.8*260=208 sampled point.I.e. the length of I/Q signal is 208.
S101: carrying out low-pass filtering by low-pass filter for the discrete I/Q signal, straight in signal for filtering out
Flow component and idling frequency.Optionally, low pass IIR filter (Low pass IIR filter) can be used and complete this step.
S200: discrete I/Q signal is subjected to sub-sampling division by N number of sub-sampling door, N number of sub-sampling door includes blood vessel
Full depth range；N is 2 or more natural numbers；Preferably, in the present embodiment, the number of sub-sampling door is to meetMaximum even number, and N number of sub-sampling door is non-cross；Due to vessel depth be far longer than it is super
Ping wave wavelength, it can be considered that the gate-width of each sub-sampling door is impulse wave wavelength in the present embodiment；Sub-sampling door
The advantages of number is even number is the display for facilitating calculating and image in subsequent process, preferably symmetrically divides vessel depth,
Respectively there are N/2 sub- sampling gates from blood vessel center to two sides.
After the division of this step sub-sampling, the sampled point formula that includes in each sub-sampling doorIt obtains
, wherein m is the pulse signal number for including in the impulse wave for detection, is 1 or more natural number, FsIt is sample frequency,
FcIt is the centre frequency of pulse signal, for each pulse signal, sampling number=sample frequency in each wavelength/
(2* signal center frequency)；Therefore for the impulse wave comprising m pulse signal, the length of group sampling gate is signal wave
When long, the discrete sampling points for including in each sub-sampling door are
S300: compound, wall filter filtering, frequency domain by the I/Q signal sequence progress time-domain signal in each sub-sampling door
Conversion generates frequency-region signal；The purpose for using wall filter to be filtered is the low velocity flow information and low speed in proposition signal
Histokinesis's information, to improve the signal-to-noise ratio of succeeding spectral signal.
The time-domain signal is compound to use formula sk(i)=∑ s (i, k) is carried out, and wherein i indicates I/Q signal in time
Discrete serial number, k is the serial number of sub-sampling door；S (i, k) indicates the IQ original signal at i moment in k-th of sub-sampling door, sk(i)
Indicate the signal after time-domain meets operation.
It is to be realized using Fast Fourier Transform (FFT) that I/Q signal, which is converted to frequency-region signal, specific formula are as follows:Wherein, W indicates the window size of Short-time Window Fourier transformation,It indicates to turn
Frequency-region signal after changing.
S400: it is imaged after calculating amplitude spectrum in the frequency-region signal obtained；The amplitude spectrum passes through formulaIt obtains.
S401: contrast is improved to the spectral image that S400 is obtained；Amplitude spectrum by being compound behaviour by it on frequency domain
It realizes, realizes formula are as follows: P (t, ω)=∑ Pk(t,ω).After the composition operation on frequency domain, it can make intravascular
The amplitude spectrum contrast of each depth is obviously improved, and can also effectively inhibit noise, is improved frequency spectrum signal-to-noise ratio, is effectively enhanced
Frequency spectrum detail resolution had truly both inhibited noise or had promoted frequency spectrum detail resolution.
S402: the S401 image obtained is further smoothed, compression processing.
The image obtained by above-mentioned steps includes the blood flow information of each depth of blood vessel, such as intravascular any depth simultaneously
Degree, the blood speed information at profound meaning moment；It can be shown according to above- mentioned information according to such as figure such as Fig. 2 a, Fig. 2 b, be divided into a-quadrant, B area
(noticing that B area is not the B-mode imaging being mentioned above), the region C, the region D (pay attention to the region D not equivalent to above
The D mode imaging mentioned) four regions are shown blood flow information, wherein and the segmentation axis of a-quadrant and B area is speed axis,
Its unit is cm/s；The segmentation axis in B area and the region D is time shaft, and the segmentation axis in the region C and the region D is vessel depth axis；A
The segmentation axis in region and the region D is vessel depth axis；Specifically, for the P of acquisitionk(t, ω) signal, k characterization therein are adopted
Sample door serial number, for expressing depth information, t is serial number time, information expression time, and frequency serial number expresses velocity information；Meanwhile
The B area frequency spectrum operated by the frequency multiplexed of S401 (time and speed (frequency) are composed)；When time t, then A can be obtained
Region frequency spectrum (depth and normal-moveout spectrum) can observe the spectral image of different moments by adjusting；Meanwhile by all speed
Average, acquisition is exactly the region D frequency spectrum (reference axis is depth and time, and amplitude is average speed).
Specifically, a-quadrant displaying is the blood flow velocity distribution profile of intravascular each depth, horizontal axis indicates vessel depth, indulges
Axis indicates blood flow velocity distribution in blood vessel；Characterize blood flow velocity the longitudinal axis (the segmentation axis of a-quadrant and B area) on 0 coordinate not
Positioned at the point of intersection with horizontal axis, and it is above the intersection point with horizontal axis, is flowed to this is because the blood in blood vessel exists with main blood flow
Opposite inverse blood flow；For the blood flow for distinguishing opposite course, optional different colours characterize different blood flow flow directions, such as main blood flow
Direction is using red characterization, and inverse blood flow is using blue characterization；Generally, such as in certain depth (such as apart from the closer depth of vascular wall
Degree) there is excessive inverse blood flow, show that vascular wall has protrusion, hardening or other hidden danger.Using blood provided by the invention
Stream speed measurement method can obtain the blood flow information of the full depth bounds of blood vessel, avoid the occurrence of in the prior art, due to the son of doctor
Sampling window is too small, the average blood speed in collected sub-sampling window because depth is not right, and fail show bleeding speed it is non-just
The case where normal adverse current.
B area displaying is the blood flow frequency spectrum of a certain designated depth, and horizontal axis characterizes the sampling time, and the longitudinal axis characterizes Hemodynamic environment
Degree；The designated depth that B area is shown is the depth of triangle arrow meaning on a-quadrant horizontal axis and the region the D longitudinal axis；That is, user can
Arrow locations on dragging a-quadrant horizontal axis or the region the D longitudinal axis as needed, to adjust specific vessel depth that B area is shown
Blood flow frequency spectrum；The blood fast time point of vertical line characterization a-quadrant in B area, that is, what a-quadrant was shown is always B area vertical line L institute
Time point blood vessel depth blood speed information.
The region D is M-Color Mode blood flow frequency spectrum, and horizontal axis characterizes the sampling time, and the longitudinal axis characterizes vessel depth.
The region C is message display area domain, shows the depth value of a-quadrant horizontal axis and the region D longitudinal axis upward arrow meaning in detail.
Fig. 3 a is the three-dimensional model diagram of each deep blood flow speed of blood vessel, and the displaying for visual pattern is detected intravascular each
Depth is in the blood speed information of each sampling time section, and Fig. 3 b is then each administrative division map in three-dimensional model diagram and Fig. 2 a, Fig. 2 b in Fig. 3 a
As association signal.The blood flow velocity 3-D graphic in cuboid phenogram 2a in Fig. 3 b, three of the cuboid are mutually perpendicular to
Side axis characterize time shaft, blood speed axis and depth axis respectively, therefore the a-quadrant view in Fig. 2 a is really rectangular shown in Fig. 3 b
The cross-sectional view of body interface；B area view is really the side cross-sectional, view of cuboid shown in Fig. 3 b；And D area view is figure
The top cross-sectional view of cuboid shown in 3b.
The image as shown in Fig. 4 a, Fig. 4 b, including the region E, the region F and the region G can also be formed；In the region E, tradition is shown
Blood flow information measurement result, such as VS: heart contraction blood flow velocity, VD: diastolic flow speed, VM: average speed of blood stream,
HR: heart rate, PI: drag index, RI: pulsating index, S/D: diastole shrinkage ratio, VFC: blood flow, it is preferred that above-mentioned parameter
It is the average value during measurement；
The 5th image shown in the region F is the wave of arbitrary parameter at any time in the 4th image selected according to user
It is dynamic, the specific variation of any parameter at any time can be expressed, can avoid, mean value is brought to the piece in diagnosis in the 4th image
Face information can also carry out the certain special diseases of auxiliary diagnosis by the changing rule of observation curve, such as heart murmur is suffered from
For person, average value shown in the 4th image cannot effectively show symptom, but the 5th image can find out its heart easily
Obvious heart rate jump at any time.
The jitter value of each parameter in the 6th image in the region GWherein, u is the parameter
Average value during measurement shown in the 4th image, xiFor the measurement sampled value of parameter at a certain moment.
Embodiment 2: as shown in figure 5, the present embodiment provides a kind of blood flow flow-measuring methods based on ultrasound；Comprising as follows
Step:
S100: it receives acquisition and is tested endovascular feedback radiofrequency signal certainly, and by the radiofrequency signal through Hilbert transform
After the step of obtaining discrete I/Q signal；The feedback radiofrequency signal is the pulsed ultrasonic wave emitted according to predetermined pulse repetition rate
Feedback radiofrequency signal after being detected to blood vessel.
In this step, the following formula of process for obtaining discrete I/Q signal by Hilbert transform is expressed:
Wherein, FcIt is the centre frequency of each pulse signal in impulse wave, FsIt is sample frequency, NnumBelieve for the radio frequency of acquisition
Number length, i.e., the number of collected discrete signal from blood vessel；Such as, when sample frequency is that (each second samples 20M to 20MHz
A sampled point) when, the rate of sound wave pulse wave is 1540m/s (spread speed of sound in human body), then in sampling frequency
It is per cm to have 260 sampled points under rate, it is assumed that arteria carotis width is 0.8cm, then at this point, the length of the radiofrequency signal of acquisition
Spend Nnum=0.8*260=208 sampled point.I.e. the length of I/Q signal is 208.
S101: carrying out low-pass filtering by low-pass filter for the discrete I/Q signal, straight in signal for filtering out
Flow component and idling frequency.Optionally, low pass IIR filter (Low pass IIR filter) can be used and complete this step.
S200: discrete I/Q signal is subjected to sub-sampling division by N number of sub-sampling door, N number of sub-sampling door includes blood vessel
Full depth range；N is 2 or more natural numbers；Preferably, in the present embodiment, the number of sub-sampling door is to meetMaximum even number, and N number of sub-sampling door is non-cross；Due to vessel depth be far longer than it is super
Ping wave wavelength, it can be considered that the gate-width of each sub-sampling door is impulse wave wavelength in the present embodiment；Sub-sampling door
The advantages of number is even number is the display for facilitating calculating and image in subsequent process, preferably symmetrically divides vessel depth,
Respectively there are N/2 sub- sampling gates from blood vessel center to two sides.
After the division of this step sub-sampling, the sampled point formula that includes in each sub-sampling doorIt obtains
, wherein m is the pulse signal number for including in the impulse wave for detection, is 1 or more natural number, FsIt is sample frequency,
FcIt is the centre frequency of pulse signal, for each pulse signal, sampling number=sample frequency in each wavelength/
(2* signal center frequency)；Therefore for the impulse wave comprising m pulse signal, the length of group sampling gate is signal wave
When long, the discrete sampling points for including in each sub-sampling door are
S300: compound, wall filter filtering, frequency domain by the I/Q signal sequence progress time-domain signal in each sub-sampling door
Conversion generates frequency-region signal；The purpose for using wall filter to be filtered is the low velocity flow information and low speed in proposition signal
Histokinesis's information, to improve the signal-to-noise ratio of succeeding spectral signal.
The time-domain signal is compound to use formula sk(i)=∑ s (i, k) is carried out, and wherein i indicates I/Q signal in time
Discrete serial number, k is the serial number of sub-sampling door；S (i, k) indicates the IQ original signal at i moment in k-th of sub-sampling door, sk(i)
Indicate the signal after time-domain meets operation.
It is to be realized using Fast Fourier Transform (FFT) that I/Q signal, which is converted to frequency-region signal, specific formula are as follows:Wherein, W indicates the window size of Short-time Window Fourier transformation,It indicates to turn
Frequency-region signal after changing.
S400: it is imaged after calculating amplitude spectrum in the frequency-region signal obtained；The amplitude spectrum passes through formulaIt obtains.
S500: t is calculated according to amplitude spectrumjThe blood flow velocity distributed intelligence at moment
Wherein, ViIndicate tjK-th of sub-sampling door amplitude spectrum P of momentk(T, ω) corresponding blood speed；；
S600: by blood flow velocity distributed intelligence V (k, tj) integral obtain blood flow flow
Discrete representation isWherein, r is sub-sampling gate-width degree, and R is tested vessel radius,
It preferably, can be by the way that whole sub-sampling doors be symmetrically divided into the present embodimentWithTwo parts,Then pass through formulaMeter
It calculates.
S601: angle modification is carried out to blood flow flow；Revised blood flow flowS indicates single
At the contraction moment of systolic cycle, d is indicated but the diastole moment of systolic cycle, α indicate vascular wall and sub-sampling door it
Between angle.Fig. 6 is the blood flow flow illustrated example corresponding with time of measuring being calculated.
S602: blood flow flow jitter index, blood flow flow jitter index are calculatedWherein
NhFor cardiac cycle number, xiIndicate that the blood flow flow during blood flow flow when single cardiac cycle number, u are entire measurement is average
Value, when the value of Index may indicate that whether blood flow flow stable, e.g., when Index is larger (be greater than 90,100 or
120；It is determined depending on concrete condition, empirical value is to take 100), it is believed that blood flow instability of flow；Fig. 7 is the blood being calculated
Flow flow illustrated example corresponding with the heartbeat period.
It should be noted that stream clock calculation is not interfere with each other with blood flow flow rate calculation.
Claims (8)
1. a kind of blood flow velocity measurement method based on ultrasound,
It is tested endovascular feedback radiofrequency signal certainly comprising receiving acquisition, and the radiofrequency signal is obtained after Hilbert transform
The step of discrete I/Q signal；
It is characterized in that, also comprising the following steps:
Discrete I/Q signal is subjected to sub-sampling division by N number of sub-sampling door, N number of sub-sampling door includes all deep of tested blood vessel
Spend range；N is 2 or more natural numbers；
I/Q signal sequence in each sub-sampling door is subjected to compound time-domain signal, wall filter filtering, frequency domain conversion, is generated
Frequency-region signal；
Amplitude spectrum is calculated from the frequency-region signal obtained, and therefrom calculates flow speed；
The number N of sub-sampling door determines by vessel depth and impulse wave wavelength, i.e.,
The number of sub-sampling door takes qualified maximum even number；
The size of sub-sampling door is by formulaIt obtains, wherein m is the pulse for including in the impulse wave for detection
Signal number is 1 or more natural number, FsIt is sample frequency, FcIt is the centre frequency of pulse signal.
2. blood flow velocity measurement method as described in claim 1, which is characterized in that the time-domain signal is compound to use formula
sk(i)=∑ s (i, k) is carried out, and wherein i indicates the discrete serial number of I/Q signal in time, and k is the serial number of sub-sampling door；s(i,
K) I/Q signal at i moment in k-th of sub-sampling door, s are indicatedk(i) signal after time-domain composition operation is indicated.
3. blood flow velocity measurement method as claimed in claim 2, which is characterized in that the step of frequency domain is converted is using short
When window Fast Fourier Transform (FFT) realize, specific formula are as follows:Wherein, w is indicated in short-term
The window size of window Fast Fourier Transform (FFT),Frequency-region signal after indicating conversion；
In the step of obtaining amplitude spectrum imaging, the amplitude spectrum passes through formulaIt obtains.
4. blood flow velocity measurement method as claimed in claim 3, which is characterized in that calculate amplitude from the frequency-region signal obtained
After frequency spectrum, further include the steps that improving spectrum contrast；Amplitude spectrum by being done composition operation realization by it on frequency domain, in fact
Existing formula are as follows: P (t, ω)=∑ Pk(t,ω)；
After the radiofrequency signal is converted to I/Q signal, further include the steps that low-pass filtering is for filtering out letter by low-pass filtering
DC component and idling frequency in number；
After calculating amplitude spectrum imaging in the frequency-region signal obtained, further include the steps that picture smooth treatment, compression processing.
5. a kind of blood flow flow-measuring method based on ultrasound, which is characterized in that comprising as described in any one of Claims 1-4
Blood flow velocity measurement method；Further include:
T is calculated according to amplitude spectrumjBlood flow velocity distributed intelligence V (k, the t at momentj) the step of；
By blood flow velocity distributed intelligence V (k, tj) integrate the step of obtaining blood flow flow.
6. blood flow flow-measuring method as claimed in claim 5, which is characterized in that calculate t according to amplitude spectrumjThe blood at moment
Flow velocity flow profile information V (k, tj) use following formula:Wherein, ViIndicate tjMoment kth
A sub- sampling gate amplitude spectrum Pk(T, ω) corresponding blood speed；
In the step of blood flow velocity distributed intelligence V (k, T) integral is obtained blood flow flow, blood flow flow:Discrete representation isWherein, r is sub-sampling
Gate-width degree, R are tested vessel radius.
7. blood flow flow-measuring method as claimed in claim 6, which is characterized in that further include carrying out angle to blood flow flow to repair
Positive step；Revised blood flow flowWherein, wherein s indicates the heart in single heartbeat period
It shrinks the moment, d indicates that the diastolic time in the heartbeat period, α indicate the angle between vascular wall and sub-sampling door.
8. blood flow flow-measuring method as claimed in claim 7, which is characterized in that further include calculating blood flow flow jitter index
The step of, blood flow flow jitter indexWherein NhFor cardiac cycle number, xiIndicate single heart week
Blood flow flow when issue, u are the blood flow flow average value during entirely measuring.
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| CN106955098B (en) * | 2017-05-05 | 2020-10-16 | 飞依诺科技(苏州)有限公司 | Blood vessel flow velocity calculation method and device |
| CN108186050B (en) * | 2018-01-03 | 2021-02-23 | 声泰特（成都）科技有限公司 | Doppler blood flow velocity imaging method and system based on ultrasonic channel data |
| CN109044324B (en) * | 2018-06-20 | 2021-11-19 | 博动医学影像科技（上海）有限公司 | Method and device for correcting blood flow characteristic value based on plaque position |
| CN109700452A (en) * | 2018-12-06 | 2019-05-03 | 河北科技大学 | A kind of velocity of blood flow distribution measurement method of limbs |
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| CN112515704B (en) * | 2020-12-01 | 2022-07-19 | 声泰特（成都）科技有限公司 | Blood vessel hardness measuring method based on ultrasound |
| CN114723684B (en) * | 2022-03-22 | 2023-03-24 | 推想医疗科技股份有限公司 | Model training method and device, and vascular structure generation method and device |
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