WO2006002625A1 - Estimation de vitesse spectrale au moyen de fonctions d'autocorrelation pour series de donnees eparses - Google Patents

Estimation de vitesse spectrale au moyen de fonctions d'autocorrelation pour series de donnees eparses Download PDF

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Publication number
WO2006002625A1
WO2006002625A1 PCT/DK2005/000392 DK2005000392W WO2006002625A1 WO 2006002625 A1 WO2006002625 A1 WO 2006002625A1 DK 2005000392 W DK2005000392 W DK 2005000392W WO 2006002625 A1 WO2006002625 A1 WO 2006002625A1
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Prior art keywords
pulses
group
velocity
series
transmitting
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PCT/DK2005/000392
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English (en)
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Jørgen Arendt JENSEN
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Danmarks Tekniske Universitet
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Publication of WO2006002625A1 publication Critical patent/WO2006002625A1/fr

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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
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8979—Combined Doppler and pulse-echo imaging systems
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/13—Tomography
    • 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
    • G01S15/02—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems using reflection of acoustic waves
    • G01S15/50—Systems of measurement, based on relative movement of the target
    • G01S15/58—Velocity or trajectory determination systems; Sense-of-movement determination systems
    • G01S15/582—Velocity or trajectory determination systems; Sense-of-movement determination systems using transmission of interrupted pulse-modulated waves and based upon the Doppler effect resulting from movement of targets

Definitions

  • the invention relates to an apparatus for determining the velocity distribution for a remotely sensed object using ultrasound and at the same time display an image of the object under in ⁇ vestigation.
  • the data acquisition is done by sending ultrasound pulses for velocity estimation and image acquisition inter-spaced in a deterministic or random order.
  • the velocity distribution is determined from the autocorrelation function of the sparse signal sequence for velocity esti ⁇ mation, and the ultrasound image is displayed from the intervening emissions.
  • a high velocity range and image frame rate can hereby be maintained.
  • the corresponding audio signal can also be regenerated from the estimated spectrum.
  • Medical ultrasound systems can be used for finding the blood and tissue velocity within the body [I]. This is done by emitting a pulse consisting of a number of sinusoidal oscillations, and then measure the scattered signal returned from the blood or tissue. The measurement is repeated a number of times, and data are sampled at the depth of interest in the tissue yielding one sample per pulse emission.
  • the frequency of the received sampled signal is proportional to the velocity of the object along the ultrasound beam and is given by:
  • v is the velocity vector
  • ⁇ is the angle between the ultrasound beam and the velocity vector
  • c is the speed of sound
  • / 0 is the emitted ultrasound frequency.
  • the velocity distribution for a given spatial position over time can be found by focusing the ultrasound beam at the position of interest.
  • the received RF data is Hubert transformed to give the in-phase and quadrature component.
  • the data is sampled at the depth of interest to give the complex signal y(i), where i is the pulse emission number.
  • a Fourier transform is then 5 performed on the sampled data.
  • the power spectrum corresponds to the velocity distribution, and the short time Fourier transform displayed over time reveals the temporal variation of the velocity distribution.
  • the sampled data used for determining the velocity distribution has a sampling frequency of: 0 where d is the depth of interrogation.
  • the Fourier transform of the data is performed on short segments of data consisting of usually 128 or 256 samples to capture the frequency variation over time of the signal.
  • a Hanning s window is often applied on the data and the fast Fourier transform is then performed.
  • An estimate of the power spectrum Py(J) of the sampled complex signal y( ⁇ for a rectangular window is
  • a B-mode image should be shown at the same time for orientation and selection of the 5 point of interest, and time must be spend on acquiring this image. This can either be done by acquiring the B-mode data interleaved with the velocity data or by acquiring a full B-mode image over a time interval.
  • the first approach will only make every second emission useful for velocity estimation, and this will reduce the sampling frequency by a factor of 2 and reduces the maximum velocity v max by a factor of 2.
  • the second approach introduces periods, where no o velocity estimation can be made, since data is not acquired, and the true velocity variation can therefore not be followed.
  • the components in the measured signal will lie in the audio range.
  • the sound of the measured signal is, thus, often 5 played. This is a problem in the second approach, where there are gaps in the audio stream. This will easily be perceived by the human ear, and the signal cannot be used for faithful audio reproduction.
  • this object is achieved by an apparatus, that acquires a sparse sequence of sampled data, and then uses an autocorrelation estimator and a Fourier transform 5 for determine the velocity distribution. This makes is possible to keep the highest attainable velocity equal to the theoretical maximum, at the same time as a B-mode image can be acquired using part of the sparse data sequence.
  • the invention can also be used for reconstructing the audio signal.
  • the limit on maximum velocity can also be exceeded by using a cross-correlation estimator to o find the mean velocity and then adjust the velocity distribution according to this estimate.
  • the invention relates to a method of estimating a velocity of tissue or of a fluid in a fluid vessel inside a person or an animal, the method comprising:
  • the transmitting step comprises intermittently transmitting series of one or more pulses o from the first group and one or more pulses from the second groups and wherein
  • At least one series of pulse(s) from the first group comprises at least two neighbouring pulses
  • the estimating step comprises:
  • images may be provided while providing the basis for determining the velocity of the tissue or fluid, such as in a predetermined position in the image.
  • Images are normally generated on the basis of pulses from a number of the series of pulses of the second group, and the velocity estimate may be provided simultaneously from the information provided by the pulses of the first group being spread over the same period of time. 5
  • the maximum ve ⁇ locity determinable is determined by the time spacing of neighbouring pulses used for that determination. Requiring that at least sometimes, such as at least each predetermined period of time, two pulses of the first group are neighbouring, the maximum velocity determinable is determined by the time period between the pulses.
  • the velocity estimation com- prises providing the estimate using an autocorrelation function based on the information of the pulses of the first group, the information at the points in time where pulses of the second group are transmitted may be reconstructed if desired.
  • the fluid velocity within a fluid vessel such as an artery or a vein, will differ from 5 the sides of the vessel to the centre thereof. Also, constrictions or the like may be interesting phenomena to investigate.
  • the providing of the image helps the positioning of the transmitting means, so that the correct estimate of the velocity is obtained.
  • the pulses transmitted into the person or animal are normally transmitted as equidistantly in time as possible. Small 0 variations may, however, occur due to delays etc in the equipment.
  • this mathematical algorithm may provide velocity estimation or data as if all pulses transmitted s were of the first group, i.e. as if no image data was provided.
  • the desired output is a velocity spectrum illustrating the full spectrum of theomme ⁇ gated moving object (tissue of fluid).
  • the step of estimating the power spectrum may comprise estimating the Fourier Trans ⁇ form of the autocorrelation function.
  • Another desired output of the estimation is an audio signal relating to the velocity of the fluid/tissue. In the present manner, this may be provided by, continuously or repeatedly:
  • the sound generation is varied by keeping estimating new filters when a new autocorre ⁇ lation function is calculated.
  • the initial signal normally is noise, such as white noise, but any signal may be used that contains frequencies in the band in which the audio signal is to be constructed. o Consequently, in the cause of varying velocity, the autocorrelation function will vary, varying the filter and consequently varying the audio signal provided to the user.
  • the step of calculating the autocorrelation function on a first set of pulses, the set comprising a predetermined number 5 of pulses of the first group comprises:
  • the step of estimating the velocity spectrum may further comprise the steps of either determining a mean value of the pulses of the first group and removing the mean value from the pulses or o determining a DC value of the velocity spectrum and removing the DC value from the velocity spectrum.
  • the overall providing or transmitting of the pulses into the person or animal may be s chosen in a number of manners, as long as the overall limits are honoured.
  • two neighbouring pulses should be of the first group and the "pauses" between series of pulses of the first group should not be too long, such as no longer than 10% of the predetermined number, preferably no longer than 1% of the predetermined number, such as down to 1-3 pulses.
  • the number of pulses in each series of pulses needs not be the same. This is, o however, a simple manner of providing the pulses.
  • the transmitting step comprises repeating a number of the intermittent series of pulses.
  • a number of series may be determined and then simply repeated.
  • the transmitting step comprises transmitting, as a series of pulses from 5 the first group, a series comprising a randomly selected number of pulses from the first group.
  • each series of pulses of the first group will have a randomly selected number of pulses.
  • the transmitting step may comprise transmitting, as a series of pulses from the second group, a series comprising a randomly selected number of pulses from the second group.
  • the series of pulses of the second group may be randomly selected, as long as they remain below the maximum number of pulses.
  • the pulses forming the basis of the images are provided in a number of directions, where after the image may be generated on the basis of the pulses received from those directions.
  • the pulses used for determining the velocity are transmitted into and received from a single direction toward the vessel or tissue.
  • the step of providing the image comprises providing the image from pulses received from each of a plurality of directions inside the person or animal, and wherein the transmitting step comprises transmitting the pulses of the first group in a predetermined direc- 0 tion into the person or animal and each pulse of the second group into one of the plurality of directions.
  • a pulse of the first group is transmitted during a first period of time and the step of receiving a pulse comprises receiving a part of the pulse during a period of time being at least the first period of time and being delayed a predetermined period of time from the transmission s thereof.
  • the delay relates to the depth of the interesting tissue/vessel in the person or animal.
  • this delay may be changed depending on the actual application.
  • the received pulse is sampled or received only a fraction of the time duration of the actual pulse (as defined by the time duration at launch/transmission).
  • the ratio between the number of pulses (within a given period of time or number of pulses) of the first and second groups may be more or less freely determined - and may actually vary
  • an interesting embodiment is one comprising the steps of:
  • the transmitting step firstly transmitting intermittent series of pulses of the first and second 0 groups with a first ratio of the number of pulses of the first group to the number of pulses of the second group and
  • the transmitting step next transmitting intermittent series of pulses of the first and second groups with a second ratio of the number of pulses of the first group to the number of pulses of the second group, the first and second ratios being different.
  • the ratio of the number of pulses of the first group to the number of pulses of the second group determines the frequency of the providing of the images and the precision of the determination of the velocity spectrum or the generation of the corresponding sound.
  • a high ratio of pulses of the second group may be desired initially in order to obtain a high frequency of images in order to position the ultrasound transceiver correctly in relation to the tissue/vessel, where after the ration may be altered to emphasize the pulses of the first group to obtain a better velocity estimation.
  • the invention in a second aspect, relates to an apparatus for estimating a velocity of tissue or a fluid in a fluid vessel inside a person or an animal, the apparatus comprising: - means for transmitting a plurality of ultrasound pulses into the person or animal in a direction toward the vessel or tissue, the pulses being at least substantially equidistant in time,
  • the transmitting means comprises means for intermittently transmitting series of one or more pulses from the first group and one or more pulses from the second groups and further s being adapted to
  • the means for estimating the velocity comprise means for:
  • the transmitting means and the receiving means are provided in one and the same ultrasound transmitter, which is a known instrument.
  • the estimating means are adapted to estimate the power spectrum on the basis of a Fourier Transform of the autocorrelation function.
  • the o audio signal providing means comprising means for, continuously or repeatedly:
  • a new filter may be generated, whereby the provided audio signal will alter with altering autocorrelation and thereby altering velocity.
  • An especially interesting manner of calculating the autocorrelation is one where the means for calculating the autocorrelation function are adapted to calculate the autocorrelation function on a first set of pulses, the set comprising a predetermined number of pulses of the first set, by: - providing a super set comprising the first group of pulses and a number, corresponding to the predetermined number, of subsequent pulses of the first group,
  • the second set of pulses being shifted k pulses, within the super set, in relation to the first set of pulses, and
  • the estimating means may further be adapted to either determine a mean value of the pulses of the first group o and remove the mean value from the pulses or determine a DC value of the velocity spectrum and remove the DC value from the velocity spectrum.
  • the transmitting means may simply repeat transmitting the same series of pulses of the first group intermittently with the same series of pulses of the second group.
  • the transmitting means may be adapted to repeat a number of the intermittent s series of pulses.
  • a more complex pattern of the series may be provided while keeping the method simple.
  • the means for providing the image is adapted to provide the image from pulses received from each of a plurality of directions inside the person or animal, and wherein the transmitting means are adapted to provide the pulses of the first group in a predetermined di- 5 rection into the person or animal and each pulse of the second group into one of the plurality of directions.
  • This type of ultrasound transmitter normally comprises an array of ultrasound transmitting el ⁇ ements, and means for phase shifting the signal for each element in the array in order to direct the ultrasound in the direction desired.
  • This known type of transducer is well suited for the o present purpose.
  • An interesting reception strategy is one where the transmitting means are adapted to transmit a pulse of the first group during a first period of time and wherein the receiving means are adapted to receive a part of the pulse during a period of time being at least the first period of time and being delayed a predetermined period of time from the transmission thereof.
  • an interesting embodiment is one further comprising means for receiving information relating to a ratio of the number of pulses to be provided of the first group to the number of pulses of the second group, and wherein the transmitting means are adapted to transmit o intermittent series of pulses of the first and second groups with a received ratio of the number of pulses of the first group to the number of pulses of the second group.
  • the ratio receiving means may be operated in order to actually emphasize more on the pulses of the first group (transmit more pulses of the first group per unit time), whereby the frequency of image generation is lowered and the precision of the velocity estimation is increased.
  • Fig. 1 shows schematically a block diagram of the main components of the system.
  • Fig. 2 shows a typical result from a traditional spectral estimation and the result for a velocity determination using the new approach.
  • Fig. 1 is shown an example of a preferred embodiment of an apparatus according to the invention.
  • This embodiment of the invention has its application within diagnostic medical ul- trasound.
  • a typical example is the determination of blood flow in peripheral vessels such as arteries in an arm, a leg, or in the carotid artery or the determination of tissue velocity.
  • the power spectrum of a stochastic signal is formally calculated from the Fourier transform of the autocorrelation function R y ⁇ k) as:
  • An estimate of the autocorrelation can be calculated by:
  • the autocorrelation function calculated by (7) is found by correlating all samples in the sig ⁇ nal segment y(i) with a time shifted version y(i + k) of the signal. It is, however, possible to calculate the correlation estimate even if some of the samples in the signal are missing. The correlation is then calculated with fewer values, and this will result in an increased standard deviation of the estimate.
  • the variance of the estimate is inversely proportional to the number of independent values, which here is proportional to N — k. Having M(k) missing values will increase the variance by a factor (N — k)J(N — k — M(k)). Keeping M(k) moderate compared to N will, thus, give a moderate increase in variance.
  • the overall variance of the spectral estimate will be determined by the lag values with the highest variance, and therefore is should be ensured that M(k) roughly has the same value for all k.
  • the missing values in the sparse sequence can be used for e.g. B-mode emissions, so that a B- mode image can be acquired simultaneously with the velocity data.
  • An example of a sequence is:
  • V V b V V b ... k l V V b V V b ... b V V b V v ...
  • the frame rate can be lowered by inserting more flow emissions between each B-mode emis ⁇ sion, and the B-mode frame rate can therefore easily be selected.
  • Other sequences can put more emphasize on the B-mode imaging to increase frame rate at the drawback of an increased variance of the spectral estimate.
  • the interleaved emissions can also be used for color flow mapping, which also can be found from sparse sequences.
  • a 50%-50% sequence can also be used to make two spectral estimates at the same time with full velocity range.
  • the sequence could for example be determined by using a white, random signal x(n) with a rectangular distribution between zero and one.
  • the ratio between flow and B-mode emissions is then determined by Pf and 1 — Py, respectively. It has to be ensured that the autocorrelation can be found for all lags as explained above.
  • the advantage of this approach is that noise, that might be repetitive with the deterministic firing sequence, is spread out over the full spectrum, and that the time division between flow estimation and B-mode imaging can be precisely tailored to the need using Pf. 5.3 Averaging RF data
  • the pulse emitted for velocity estimation will in general have a number of sinusoidal oscilla ⁇ tions to keep the bandwidth small and increase the emitted energy.
  • the received signal is then correlated over the pulse duration, and applying a matched filter to increase the signal-to-noise ratio will increase the correlation to a duration of roughly two pulse lengths.
  • This data can also be used in calculation of the autocorrelation as: i N r -l N ⁇ k-l
  • *#> (ff _ w _ M , )W ⁇ ⁇ ⁇ /+*. ⁇ y ( /+*.'+* ) . r ⁇
  • j is the RF sample index
  • J ⁇ is the index for the depth of the range gate start
  • N r is the number of RF samples.
  • the measured signal will often contain large signal components around low frequencies em ⁇ anating from the tissue, especially near the vessel wall. These signals can be removed if they 0 obscure the blood velocity signal and makes its spectral visualization difficult. This can be done either in the time or the frequency domain.
  • the first approach is to take the mean value of the signals and subtract that. The mean signal as a function RF sample number j is found from
  • ysM (N-M(Jc)) to yUJ) ' (14) where y sta (j) is the estimated stationary signal. Missing RF signals are replaced by zeros in the 5 sum. The estimated stationary signal is then subtracted from y(j, ⁇ ) to remove a fully stationary component. This should be done before the autocorrelation function is calculated.
  • the stationary echo canceling can also be performed by fitting a first or higher order polynomial to the data using e.g. a least squares fit.
  • the polynomial will only be fitted to the data, that has been measured.
  • the values for the polynomial is then subtracted from this data in order to o remove the stationary component.
  • This processing can also be performed in the frequency domain.
  • the cut-off frequency in the spectrum should be determined from the velocity of the tissue surrounding the blood vessel using (1).
  • the audio signal can be regenerated from the estimated autocorrelation function.
  • e(n) models the many random and independent red blood cells in the vessel.
  • h(n;n) models the velocity spectrum at the given time.
  • the filter is time varying, since the velocity and thereby frequency content varies over the cardiac cycle.
  • the autocorrelation of this is
  • jF ⁇ denotes Fourier transform and IT ""1 ! ⁇ inverse Fourier transform.
  • a window can s be applied to the impulse response to reduce edge effects. It is also appropriate to mask out small amplitude values in the frequency domain, since this most probably is noise from the reconstruction process.
  • the phase of the filter is neglected and only a linear phase version is reconstructed.
  • a minimum phase version could be reconstructed using a Hubert transform, but this is of no consequence, 0 since it is a stochastic signal that needs to be made.
  • the final signal is made by convolving h ⁇ (k;n) with a Gaussian, white random signal. This will be the audio signal for a given time segment, and this signal should be added to signals from other segments properly time aligned. To avoid edge effects, a window is applied on the signal segment before addition.
  • the maximum velocity, that can be estimated, is restricted by (3) due to aliasing. This is really not a restriction on the maximum velocity, but on the widest spread of velocities, where the distance between the lowest and highest velocity at any given time must be less than
  • Estimating the mean velocity and adjusting the spectrum to lie around this velocity can therefore o increase the maximum velocity range.
  • the maximum velocity can be estimated by using the cross-correlation approach developed in [2]. Two or more RF lines are then cross-correlated and the shift in time between them found. This will yield the mean velocity of the flow. The center of the spectrum is then offset to lie around this mean frequency. The same data as for the spectral estimation can be used, if a narrow pulse is emitted. The spectrum will be widened due to the wide bandwidth of the pulse, but this can be avoided by filtering the received RF data with a narrow-band pulse before calculation of the autocorrelation function. This will narrow the bandwidth and the velocity spectrum width.
  • Data beamformed along the flow direction as described in [3] can also be used for the flow estimation.
  • the received data then tracks the movement of the scatterers, and a single or narrow distribution of velocities are then found. This will give a spectrum, that is narrower than for taking data out at a range of depths.
  • Fig. 1 the specific setup of the measuring apparatus itself is indicated schematically. It com ⁇ prises a generator or pulser 1, an emit beam former 2, an array ultrasound emitting transducer 3 providing an emitted field, an array ultrasound receiving transducer 5 receiving a scattered field, a receive beam former 6, and a velocity estimator 7 for estimating the velocity spectrum.
  • the estimate is the passed on to a display 8 and to a unit 10 that reconstructs the audio sound from the spectrum.
  • the unit 9 is used for presenting the B-mode image.
  • the pulser 1 generates a pulsed voltage signal with four sinusoidal oscillations at a frequency of 2 3VIHz in each pulse, that is fed to the emit beam former 2.
  • the emit beam former 2 splits up the signal from the pulser into a plurality of signals, which are being fed to the respective elements of the emitting transducer array 3.
  • the emit beam former 2 is capable of individually attenuating and delaying the signals to each of the elements of the transducer array 3.
  • the same array transducer is used for both emitting and receiving the pulsed ultrasound field. It consists of 64 elements with an element width of 0.43 mm and a spacing between neighboring elements of 0.05 mm. The height of the elements is 5 mm.
  • the emitted field from the transducer is scattered by the blood in the blood vessel 4 and part of the scattered field is received by the array transducer, and the signals from the individual ele ⁇ ments are passed on to the receive beam former.
  • the signals from the elements are individually scaled in amplitude and individually delayed and are thereafter summed to yield a single output signal from the receive beam former focused at the depth of interest.
  • a Hubert transformation is the performed on the data to yield the in-phase and quadrature component for y(i).
  • This processing is repeated for a number of emissions. Two emissions are done for flow estima ⁇ tion and one emission can be used for making a B-mode image. A sequence with 128 emissions are made and the emissions for flow estimation are collected in the velocity estimator processor 7. The autocorrelation function of this data is calculated at the depth of interest using
  • Table 1 Standard parameters for transducer and femoral flow simulation.
  • the power spectrum of the data is then calculated by
  • the process is repeated continuously and the spectra are displayed as a gray scale image as a function of time and frequency or velocity.
  • Fig. 2 An example of results from application of the method is shown in Fig. 2. Simulated data from flow in the femoral artery has been used with the parameters shown in Table 1.
  • the RF data was obtained from simulating the flow in the femoral artery by using the Field II program [4] and the Womersley-Evans method for pulsed flow.
  • One heart cycle of pulsatile flow was simulated and the received RF signal from the array focused at the vessel was found.
  • the data were then processed using the traditional approach using a Harming window on 128 samples segments. The result is shown on the top in Fig. 2.
  • a sparse sequence was then used in the new approach, where every third received signal was replaced by zeros (v v B sequence).
  • the autocorrelation estimate was calculated using (12) and the parameters in Table 1.
  • a Harming window covering 75% of the autocorrelation function was multiplied onto it and the power spectrum found. This is shown in the bottom in Fig. 2. It can be seen that a more smooth spectrum can be found although 33% of the data is missing.

Abstract

Selon le présente invention, la distribution de vitesses du sang ou de tissu est affichée au moyen de scanners ultrasonores par détermination du spectre de puissance du signal reçu. Cette distribution s'effectue par génération d'une transformée de Fourier du signal reçu et par présentation des spectres dans un affichage de mode M. Il est souhaitable de présenter une image d'orientation en mode B et des données associées doivent être entrelacées avec le flux de données. Le spectre de puissance peut être calculé à partir de la transformée de Fourier de la fonction d'autocorrélation Ry(k), son étendue de retard k étant donnée par le nombre de l'émission N dans le segment de données pour une estimation de vitesses. Le retard correspond à la différence du nombre d'impulsions, de telle manière que, pour un retard k, des données provenant d'une émission i sont corrélées avec i + k. L'autocorrélation pour le retard k peut être mise en moyenne sur des paires N-k d'émissions. Il est possible de calculer Ry(k) pour une série éparse d'émissions, aussi longtemps que toutes les combinaisons d'émissions englobent tous les retards dans Ry(k). Une série éparse d'émissions espacées entre elles avec des émissions de mode B, peut, donc, être utilisée pour estimer Ry(k). La séquence `v B v v B! engendre deux émissions en mode 2 B (B) pour toutes les émissions de vitesse 3 (v) et une séquence 3 :2 est dénotée. Toutes les combinaisons de retards sont présentes k=`0123..!, si la séquence est répétée en continu. La variance de l'estimation de Ry(k) est déterminée par le nombre de paires d'émissions pour la valeur de k, et elle peut être abaissée par obtention d'une moyenne des données RF sur la porte en distance. Plusieurs autres séquences peuvent être élaborées avec cette propriété, à condition d'avoir 3:3, 3:4, et 5:8 ou des séquences aléatoires paires, de telle façon que peut être sélectionné le rapport entre la fréquence de trames en mode B et la précision spectrale.
PCT/DK2005/000392 2004-07-02 2005-06-15 Estimation de vitesse spectrale au moyen de fonctions d'autocorrelation pour series de donnees eparses WO2006002625A1 (fr)

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2007023438A3 (fr) * 2005-08-22 2007-05-31 Koninkl Philips Electronics Nv Systeme d'imagerie de diagnostic ultrasonore equipe d'un doppler de tissu spectral et sonore
JP2011509792A (ja) * 2008-01-22 2011-03-31 アリク ペレド， 授乳を監視するための方法および装置
WO2022229047A1 (fr) * 2021-04-28 2022-11-03 Koninklijke Philips N.V. Interface utilisateur et procédé de définition de priorité d'acquisition dans des modes d'imagerie entrelacés d'échographie

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5501223A (en) * 1994-11-23 1996-03-26 General Electric Company Dynamic firing sequence for ultrasound imaging apparatus
US5876341A (en) * 1997-06-30 1999-03-02 Siemens Medical Systems, Inc. Removing beam interleave effect on doppler spectrum in ultrasound imaging
US6423006B1 (en) * 2000-01-21 2002-07-23 Siemens Medical Solutions Usa, Inc. Method and apparatus for automatic vessel tracking in ultrasound systems

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5501223A (en) * 1994-11-23 1996-03-26 General Electric Company Dynamic firing sequence for ultrasound imaging apparatus
US5876341A (en) * 1997-06-30 1999-03-02 Siemens Medical Systems, Inc. Removing beam interleave effect on doppler spectrum in ultrasound imaging
US6423006B1 (en) * 2000-01-21 2002-07-23 Siemens Medical Solutions Usa, Inc. Method and apparatus for automatic vessel tracking in ultrasound systems

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
BASOGLU C ET AL: "Computing requirements of modern medical diagnostic ultrasound machines", PARALLEL COMPUTING, ELSEVIER PUBLISHERS, AMSTERDAM, NL, vol. 24, no. 9-10, September 1998 (1998-09-01), pages 1407 - 1431, XP004148103, ISSN: 0167-8191 *
KIRKHORN J ET AL INSTITUTE OF ELECTRICAL AND ELECTRONICS ENGINEERS: "A new technique for improved spatial resolution in high frame rate color doppler imaging", 2003 IEEE ULTRASONICS SYMPOSIUM PROCEEDINGS. HONOLULU, HAWAII, OCT. 5, vol. VOL. 1 OF 2, 5 October 2003 (2003-10-05), pages 1947 - 1950, XP010701093, ISBN: 0-7803-7922-5 *

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2007023438A3 (fr) * 2005-08-22 2007-05-31 Koninkl Philips Electronics Nv Systeme d'imagerie de diagnostic ultrasonore equipe d'un doppler de tissu spectral et sonore
JP2011509792A (ja) * 2008-01-22 2011-03-31 アリク ペレド， 授乳を監視するための方法および装置
WO2022229047A1 (fr) * 2021-04-28 2022-11-03 Koninklijke Philips N.V. Interface utilisateur et procédé de définition de priorité d'acquisition dans des modes d'imagerie entrelacés d'échographie

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