DUAL ULTRASONIC TRANSDUCER PROBE FOR BLOOD FLOW MEASUREMENT, AND BLOOD VESSEL DIAMETER DETERMINATION METHOD

Abstract: For use in a Doppler based ultrasound system (1) for blood flow measurement, a dual ultrasonic transducer probe (6) includes first and second ultrasound transducers (7, 8) whose ultrasound beams (9, 11) intercept, and which can be so disposed relative to a blood vessel's longitudinal axis (4) that both ultrasound beam axis (12, 13) intercept the bloodvessel's longitudinal axis and correspondingly subtend acute beam inclination angles theta 1 and theta 2 therewith. A blood vessel diameter determination method based on calculating a n single dimension vector of energy values Eii along an ultrasound beam having a portion L extending between the outermost surface SO and the innermost surface SI of a blood vessel's sidewall correspondingly whereby the blood vessel diameter D can be calculated according to the relationship: D=L sin theta where theta is the beam inclination angle between the ultrasound beam (9) axis and the blood vessel's longitudinal axis (4).

Description: DUAL ULTRASONIC TRANSDUCER PROBE FOR BLOOD FLOW MEASUREMENT, AND BLOOD VESSEL DIAMETER DETERMINATION METHOD FIELD OF THE INVENTION The invention relates to a dual ultrasonic transducer probe for use in a Doppler based ultrasound system for blood flow measurement and determination of associated hemodynamic parameters, and a blood vessel diameter determination method. BACKGROUND OF THE INVENTION In US Patent 4,103,679 to Aronson, there is illustrated and described a Doppler based ultrasound system for blood flow measurement in a blood vessel which requires that an ultrasound transducer array be so disposed relative to the blood vessel's longitudinal axis that a Pulse Wave multi-gated ultrasound beam emanating therefrom intercepts the blood vessel's longitudinal axis at a variable beam inclination angle θ whereby blood flow measurement can be quantitatively measured independent of the beam inclination angle. An article entitled "New, Angle-independent, Low-Cost Doppler System to Measure Blood Flow" by M. Skladany et al., The American Journal of Surgery, Volume 176, August 1998, pgs. 179 - 182, illustrates and describes a similar Doppler based ultrasound system for blood flow measurement. However, the aforementioned references neither address the practical difficulties involved with ensuring that an ultrasound beam is correctly positioned with respect to a blood vessel's longitudinal axis nor accurate measurement of a blood vessel's diameter, both factors playing a major role in an accurate blood flow measurement determination. SUMMARY OF THE INVENTION In accordance with a first aspect of the present invention, there is provided for use in a Doppler based ultrasound system for blood flow measurement in a blood vessel having a longitudinal axis, a dual ultrasonic transducer probe comprising: (a) a housing; (b) a first ultrasound transducer for transceiving a first ultrasound beam with a first ultrasonic beam axis; (c) a second ultrasound transducer for transceiving a second ultrasound beam with a second ultrasonic beam axis intersecting said first ultrasonic beam axis; and (d) a support member for supporting said first and second ultrasound transducers, said support member being rotatable about said first ultrasonic beam axis whereby said second ultrasound transducer rotates about said first ultrasonic beam axis, and said support member being displaceably mounted in said housing for displacing said first and second ultrasound transducers in tandem, the arrangement being such that both said first and second ultrasound beam axes intercept the blood vessel's longitudinal axis and correspondingly subtend acute beam inclination angles θi and Θ 2 therewith for enabling the measurement of Doppler shift frequencies along said first and second ultrasound beams. The dual ultrasonic transducer probe of the present invention facilitates manipulation of its ultrasonic transducers relative to a blood vessel such that both their ultrasonic beam axes intercept the blood vessel's longitudinal axis, and subtend acute beam inclination angles therewith. Typically, such positioning is a two step process including a first step for intercepting the blood vessel's longitudinal axis with the first ultrasonic beam; and a second step for intercepting the blood vessel's longitudinal axis with the second ultrasonic beam by rotating it relative to the first ultrasonic beam which is maintained in its intercepting position. The present invention is particularly suitable for accurate blood flow measurement in a human subject's carotid artery. In accordance with a second aspect of the present invention, there is provided a blood vessel diameter determination method comprising the steps of: (a) positioning an ultrasound transducer relative to a blood vessel such that its associated ultrasound beam axis intercepts the blood vessel's longitudinal axis and subtends an acute beam inclination angle θ therewith; (b) energizing the ultrasound transducer for insonating the blood vessel with a pulsed wave ultrasound beam; (c) receiving a n single dimension vector of Doppler shift frequency reflections along the ultrasound beam for a plurality of gates i = 1 to n therealong; (d) cyclically repeating steps (b) and (c) m times for obtaining a (m x n) two dimension matrix of energy associated values E ; (e) calculating a n single dimension vector of energy values Ej along the ultrasound beam; (f) determining the beam corrected chord length L of a portion of the ultrasound beam extending between the outermost surface So and the innermost surface Si of the blood vessel's sidewall correspondingly adjacent the ultrasound transducer, and remote therefrom; and (g) calculating the blood vessel diameter D according to the relationship: D = L sin θ. The blood vessel diameter determination method of the present invention can be implemented using either one of two approaches for calculating the n single dimension vector of energy values Ej along the ultrasound beam, and either one of two approaches for determining the portion of the ultrasound beam which intercepts the blood vessel's sidewall. The two approaches for calculating the n single dimension vector of energy values Ej are based on either time or frequency domain operations on the (m x n) two dimension matrix of energy associated values E . The two approaches for determining the portion of the ultrasound beam which intercepts the blood vessel's sidewall are based on parametric estimation for detecting initial and final parabolic like portions along the n single dimension vector of energy values Ej, and thresholding techniques. Due to the inclination of the ultrasound beam relative to the blood vessel, the beam corrected chord length L is preferably calculated according to the relationship: L = P - B/tan θ where P is a measured chord length, and B is the beam width of the ultrasound beam. BRIEF DESCRIPTION OF THE DRAWINGS For a better understanding of the present invention and to show how the same can be carried out in practice, by way of non-limiting examples, reference will be made to the accompanying drawings, in which: Figure 1 is a pictorial representation showing a system of the present invention for blood flow measurement in a human subject's carotid artery including a dual ultrasound transducer probe, and a schematic representation of his carotid artery; Figure 2A is a schematic representation showing the disposition of the probe's ultrasound transducers relative to the subject's carotid artery during blood flow measurement, and Figures 2B and 2C are respectively side and top views thereof; Figure 3 is a block diagram of a control unit of the system of Figure 1 ; Figure 4 is a pictorial representation showing a first embodiment of a partially disassembled dual ultrasound transducer probe for use with the system of Figure 1; Figure 5 is an exploded pictorial representation of the probe of Figure 4; Figure 6 is a longitudinal cross sectional view of the probe of Figure 4 along the line VI-VI therein; Figure 7 is a pictorial representation showing a second embodiment of a dual ultrasound transducer probe for use with the system of Figure 1; Figure 8 is a pictorial representation showing a third embodiment of a dual ultrasound transducer probe for use with the system of Figure 1 ; Figure 9 is a transverse cross sectional view of the probe of Figure 8 along the line IX-IX therein; Figure 10 is a flow diagram illustrating the use and operation of the system of Figure 1, and a schematic representation showing a blood vessel's cross section for illustrating one approach for blood flow measurement; Figure 11 is a pictorial representation showing a multi-gated Pulse Wave ultrasound beam intercepting a blood vessel; Figure 12 is a pictorial representation graphically showing a vector of energy values Ej along a multi-gated Pulse Wave ultrasound beam intercepting a blood vessel; Figure 13 is a pictorial representation graphically showing the gates along an ultrasound beam whose derivative energy values exceed the value of an AADTE parameter of a thresholding technique for determining the beam corrected chord length L of the portion of an ultrasound beam intercepting a blood vessel; Figure 14 is a pictorial representation graphically showing the gates along an ultrasound beam whose energy values Ej exceed the value of an AATE 5 parameter of a thresholding technique for determining the beam corrected chord length L of the portion of an ultrasound beam intercepting a blood vessel; and Figure 15 is a pictorial representation showing the graph of Figure 14 with the gates whose energy values Ej satisfy the conditions Ej > AADTE and o DETAILED DESCRIPTION OF THE DRAWINGS With reference now to Figures 1-3, there is shown a system 1 for blood flow measurement in a subject's carotid artery, and the determination of associated hemodynamic parameters. The subject's carotid artery is schematically shown as a right cylindrical duct 2 with a sidewall 3, a longitudinal 5 axis 4, a diameter D, and through which blood flows in a direction denoted A. The system includes a probe 6 containing a pair of ultrasound transducers 7 and 8 for transmitting and receiving a pair of narrow Pulse Wave (PW) multi-gated ultrasound beams 9 and 11 having a pair of ultrasound beam axes 12 and 13 which forwardly intercept at an acute intersection angle α. The ultrasound 0 transducers 7 and 8 can be moved in tandem, and the ultrasound transducer 8 can be rotated about the so-called fixed ultrasound beam axis 12 such that the directions of their ultrasound beams 9 and 11 can be readily manipulated to intercept the carotid artery's longitudinal axis 4. On such positioning, the ultrasound beams 9 and 11 subtend acute beam inclination angles θi and Θ 2 where 5 θi = Θ 2 + α with the carotid artery's longitudinal axis 4, respectively, and have beam portions 14 and 16 (shown in hashed lines in Figure 2 A) of lengths Li and L 2 , respectively, which transverse the carotid artery at diametrically opposite portions. The system 1 also includes a control unit 17 with an ultrasound generator 18 for energizing the ultrasound transducers 7 and 8, a Doppler unit 19 for measuring the Doppler shift frequency at a predetermined number of multi-gated sample volumes SVj along each of the ultrasound beams 9 and 11, and a processor 21 for determining flow related information for display on a display 22. The display 22 displays the two lengths Li and L 2 , a graph of blood flow against time, a graph of blood velocity against time, a graph of blood vessel diameter against time, a graph of representative systolic and diastolic blood flow velocity profiles, average blood flow ABF over a cardiac cycle, an index of blood vessel elasticity BVE over a cardiac cycle, an index of shear rate SR, and a time dependent distal resistance index Rs(t). The control unit 17 also includes a beeper 23 for issuing audible signals at a predetermined time in the subject's cardiac cycle, for example, at peak systole for facilitating manual set-up of the system 1. With reference now to Figures 4-9, three implementations 6A, 6B and 6C of the dual ultrasound transducer probe 6 are now described, each probe having a pair of ultrasound transducers 7 and 8 which are displaceable in tandem and whose ultrasound transducer 8 is rotatably mounted about the so-called fixed ultrasound beam axis 12. With particular reference to Figures 4-6, a dual ultrasound transducer probe 6A includes a probe housing 31 with a base plate 32, and a cover 33 consisting of a rear cover portion 33A, a front cover portion 33B, and an ultrasound transmissive window 33C. The base plate 32 rotatably supports a rectangular shaped frame 34 (constituting a support base) about a longitudinal axis 36 by a motor 37 via a straight tooth bevel gear arrangement 38. The frame 34 has a rearward directed bracket 39 for rotatably supporting a support member 41 about an axis of rotation 42 by means of a pair of bearings 43 and 44. The support member 41 carries the ultrasound transducers 7 and 8 having forwardly intercepting ultrasound beam axes 12 and 13, and is driven about the axis of rotation 42 which coincides with the ultrasound beam axis 12 by a motor 46 also supported on the bracket 39. A flexible diaphragm 47 sealing divides the interior of the probe housing 31 into two portions, a front portion 31A accommodating the ultrasound transducers 7 and 8 and filled with a suitable ultrasound transmissive substance, and a rear portion 3 IB accommodating the motors 37 and 46 (see Figure 6). A hand operated joystick 48 is provided on the probe housing 31, and is capable of a FORWARD/BACKWARD movement denoted B for correspondingly driving the motor 37 in clockwise/counterclockwise directions for correspondingly rotating the frame 34 in clockwise/counterclockwise directions denoted C, and a LEFT/RIGHT movement denoted D for correspondingly driving the motor 46 in clockwise/counterclockwise directions for correspondingly rotating the support member 41 in clockwise/counterclockwise directions denoted E. With reference now to Figure 7, a dual ultrasound transducer probe 6B is similar to the dual ultrasound transducer probe 6A, and identical parts are similarly numbered. The difference between the two probes 6A and 6B is that in the latter, the rotation of the frame 34 and the support member 41 is effected by flexible power transmission cables 49 and 51 , respectively, driven by the motors 37 and 46, respectively, which are external to the probe housing 31 whereby its size can be considerably reduced, and flexible diaphragm 47 can be dispensed with. With reference now to Figures 8 and 9, a dual ultrasound transducer probe 6C has ultrasound transducers 7 and 8 whose respective ultrasound beam axes 12 and 13 rearwardly intercept at an imaginary interception point 52 at an interception angle α such that 02 = θi + α. In this case, the ultrasound transducers 7 and 8 are mounted on a support member 53 which can be manually rotated about an axis of rotation 54 which coincides with the ultrasound beam axis 12, and which can be manually slided along a track 56. The operation of the system 1 is now described for the case that the multi-gated PW ultrasound beams 9 and 11 have 220 gates therealong each, and the system 1 is manually set-up. The probe 6 is attached to a subject's neck adjacent to his carotid artery such that both the ultrasound beams 9 and 11 transverse his carotid artery at substantially but typically not diametrically opposite portions of its sidewall 3. The ultrasound generator 18 energizes the ultrasound transducers 7 and 8 to transmit the pair of narrow PW ultrasound beams 9 and 11. The Doppler unit 19 measures the Doppler frequency shift within each of a continuous series of small sample volumes SV, along each of the ultrasound beams 9 and 11. The processor 21 detects the subject's systolic peak after a number of cardiac cycles and proceeds to activate the beeper 23. The processor 21 determines the initial beam corrected chord lengths Li and L 2 of the beam portions 14 and 16 as described hereinbelow with respect to the ultrasound beam 9 only for the sake of convenience, and displays their values on the display 22. The user notes the initial values of the lengths Lj and L2 and manipulates both the ultrasound transducers 7 and 8 in tandem in search of the maximum length Li indicating that the ultrasound transducer 7 is correctly disposed relative to the subject's carotid artery. On detection of the maximum length Li, the user proceeds to rotate the ultrasound transducer 8 in search of the maximum length L 2 whilst maintaining the ultrasound transducer 7 in the same position. The 220 gates along the ultrasound beam 9 can be divided into five distinct regions as follows: a first region Ri closest to the ultrasound transducer 7 consisting of consecutive gates (1,85) which are wholly exterior to the subject's blood vessel, a second region R 2 consisting of consecutive gates (86,90) which partially intercept the outermost surface So of the blood vessel's sidewall 3 closest to the ultrasound transducer 7, a third region R 3 consisting of consecutive gates (91,155) wholly within the subject's blood vessel, a fourth region R 4 consisting of consecutive gates (156,160) which partially intercept the innermost surface Si of the blood vessel's sidewall 3 furthermost from the ultrasound transducer 7. and a fifth region R 5 furthermost from the ultrasound transducer 7 consisting of consecutive gates (161,220) which are wholly exterior to the subject's blood vessel (see Figure 11). The measured chord length denoted P of the three intermediate regions R 2 , R3 and R4 enables determination of the beam corrected chord length L according to the relationship: L = P - B/tan 0 where B is the beam width of the ultrasound beam, and 0 is the acute beam inclination angle subtended between the ultrasound beam axis 9 and the blood vessel's longitudinal axis 4. Determination of the beam corrected chord length L is in principle a two step process, the first step being the calculation of a vector of 220 energy values Ej from a 128 x 220 matrix of energy associated values Ejj acquired over 128 excitations of the ultrasound transducer 7, and the second step being the detection of the first and last gates along the ultrasound beam 9 which intercept with the outermost surface So and the innermost surface Si of the blood vessel's sidewall 3 and are respectively adjacent the ultrasound transducer 7, and remote therefrom. The first step involves the high pass filtering of the columns of the 128 x 220 matrix of energy associated values Ejj for removing spurious low frequency noise, and thereafter performing either frequency domain operations or time domain operations. The frequency domain operations include executing a Fast Fourier Transform (FFT) on the 128 x 220 two dimension matrix of energy associated values Ejj, summing the energy values Ejj for each column j = 1 to 128 of the 128 x 220 matrix of energy associated values Ejj according to the relationship: 'll Real + E ij I in age and repeating the summation operation for each gate i = 1 to 220 along the ultrasound beam 9 so as to obtain a vector of 220 energy values Ej shown graphically in Figure 12. The time domain operations include summing the energy values Ejj for each column j = 1 to 128 of the 128 x 220 matrix of energy associated values E„. according to the above relationship, and repeating the summation operation for each gate i = 1 to 220 along the ultrasound beam 9 so as to obtain a single dimension vector of 220 energy values E, also shown in graphically in Figure 14. Alternatively, either the real part only or the imaginary part only of the energy values E for each column j = 1 to 128 of the 128 x 220 two dimension matrix of energy associated values E„ can be summed. On the basis of the vector of 220 energy values E„ two approaches can be employed for determining the measured chord length P as follows: Parametric estimation involving the detection of the first and last parabolic like portions along the vector of 220 energy values E,, or alternatively thresholding techniques. Parametric estimation is by way of examination of consecutive groups of 20 consecutive gates along the ultrasound beam 9, thereby specifying 200 consecutive groups therealong, and includes the following steps: calculating the coefficients a, b and c of the equation y = a + bE, + cE, for 200 groups of consecutive gates (i, i+20) for i = 1 to 200; calculating a leftmost boundary identification value T| e ft according to the relationship: T =- for each group of 20 consecutive gates; and determining the group of consecutive gates closest to the ultrasound transducer 7 denoted Go which has the maximum i e n value of the 200 Tι ef t values (see Figure 12). Of this group of consecutive gates Go, the outermost surface So of the blood vessel's sidewall 3 is assumed to be the group's first gate closest to the ultrasound transducer 7 which in this case is gate 85 bordering between the regions Ri and R 2 . These steps are then repeated for the gates along the ultrasound beam 9 in the reverse direction for determining the group of consecutive gates with the maximum rightmost boundary identification value T πgh t value of the again 200 T πg ht values denoted Gi (see Figure 12). Of this group of consecutive gates Gi, the innermost surface S] of the blood vessel's sidewall 3 is assumed to be the group's last gate furthermost from the ultrasound transducer 7 which in this case is gate 165 bordering between the regions R 4 and R 5 . The thresholding technique involves selecting all gates along the ultrasound beam 9 which satisfy the conditions Ej > AADTE and Ej > AATE where the value of so-called average absolute derivative threshold energy AADTE of the vector of 220 energy values Ej is calculated according to the relationship: AADTE =!∑|E 1+1 - E,| and the value of the so-called average amplitude threshold energy AATE of the vector of 220 energy values Ej is calculated according to the relationship: _ . ^^ mean of E, values + median of E, values AATE = ! ! 2 This approach may render so-called multiple humped graphs ostensibly indicating the presence of several phantom blood vessels as represented by the pair of phantom blood vessels 2 A and 2B which must be necessarily combined to render the single blood vessel 2 (see Figure 15). This can be achieved by the following algorithm: generating a g single dimension vector K of all the gates i = 1 to 220 along the ultrasound beam whose energy value Ej satisfies the conditions Ej > AADTE and Ej > AATE; generating a h single dimension vector DK where DKh = Kh+i - K h for h = 1 to g; calculating the parameter Average DK according to the relationship: Average DK = -V DK g £ϊ * determining the leftmost region of gates which satisfies the condition DKι/2 > Average DK and specifying that the leftmost gate of the leftmost region is the outermost surface So; and determining the rightmost region of gates which satisfies the condition DK h /2 > Average DK, and specifying that the rightmost gate of the rightmost region is the innermost surface Si. For example, for a vector DK h = [1,1,1,1,1,1,3,1,1,4,1,1,1,1], Avg DK = 19/14, the so-called leftmost region is where DK = 3, the so-called rightmost region is where DK = 4, the leftmost gate of the leftmost region DK = 3 is the outermost surface So, and the rightmost gate of the rightmost region DK = 4 is the innermost surface Si. After correct positioning, the processor 21 determines the beam inclination angles θi and 0 2 using the conventional Doppler equation on the assumption that an identical peak or average blood velocity is measured along both of the two ultrasound beams 9 and 11. Thereafter, based on the assumption that the blood vessel in the region of insonation has a circular cross section which changes in a radial fashion, the processor 21 continuously calculates the blood vessel's diameter D for each of the two ultrasound beams 9 and 11 according to the relationship: D = L sin 0, and averages the results for display on the display 22. Based on this measurement, the processor 21 calculates blood flow measurement according to the product of A and v avg where A is the blood vessel's cross section area and v avg is the average blood flow speed. Alternatively, blood flow measurement can be calculated according to ∑AjVj where Aj is the semi-annular cross sectional area associated with a sample volume SVj and Vj is the measured blood flow speed at a particular sample volume SVj (see Figure 10). Finally, the processor 21 determines other blood flow information for display on the display 22 as follows: First, a time dependent index of the distal resistance Rs(t) according to the relationship: Rs(,) - Pr(,) F(t) where Pr(t) is the time dependent arterial blood pressure Pr; and F(t) is the instantaneous blood flow. Second, index of shear rate at the outermost surface So and the innermost surface Si of the blood vessel ' s sidewall 3 with respect to the ultrasound probe 6 according to the relationship: dV at D =0.and D. dD And lastly, blood vessel elasticity according to the relationship: D -D, D., where D s is the blood vessel diameter at peak systole and D is the blood vessel diameter at diastole. While the invention has been described with respect to a limited number of embodiments, it will be appreciated that many variations, modifications and other applications of the invention can be made within the scope of the claims appended hereto. For example, the probes 6A and 6B can be implemented with rearwardly intercepting ultrasound beam axes as implemented in probe 6C whilst the probe 6C can be implemented with the forwardly intercepting ultrasound beam axes as implemented in the probes 6 A and 6B. Also, the manipulation of the ultrasound transducers into their correct positioning relative to a blood vessel's longitudinal axis can be performed automatically.

Claims: CLAIMS: 1. For use in a Doppler based ultrasound system for blood flow measurement, a dual ultrasonic transducer probe comprising: (a) a housing; (b) a first ultrasound transducer for transceiving a first ultrasound beam with a first ultrasonic beam axis; (c) a second ultrasound transducer for transceiving a second ultrasound beam with a second ultrasonic beam axis intersecting said first ultrasonic beam axis; and (d) a support member for supporting said first and second ultrasound transducers, said support member being rotatable about said first ultrasonic beam axis whereby said second ultrasound transducer rotates about said first ultrasonic beam axis, and said support member being displaceably mounted in said housing for displacing said first and second ultrasound transducers in tandem, the arrangement being such that both said first and second ultrasound beam axes intercept the blood vessel's longitudinal axis and correspondingly subtend acute beam inclination angles θi and 0 2 therewith for enabling the measurement of Doppler shift frequencies along said first and second ultrasound beams. 2. The probe according to claim 1 wherein said support member is rotatably mounted on a support base about said first ultrasonic beam axis, and said support base is rotatably mounted about a longitudinal axis in said housing whereby said first and second ultrasound transducers are rotatable in tandem about said longitudinal axis. 3. The probe according to claim 2 and further comprising motorized means for rotating said support member about said first ultrasonic beam axis, and said support base about its longitudinal axis. 4. The probe according to claim 3 wherein said motorized means includes a pair of motors external to said housing. 5. The probe according to any one of claims 1 to 4 and further comprising a hand operated joystick for controlling the motion of said support member. 6. The probe according to claim 1 wherein said pair of ultrasound transducers are rectilinearly displaceable in tandem in said housing. 7. A blood vessel diameter determination method comprising the steps of: (a) positioning an ultrasound transducer relative to a blood vessel such that its associated ultrasound beam axis intercepts the blood vessel's longitudinal axis and subtends an acute beam inclination angle 0 therewith; (b) energizing the ultrasound transducer for insonating the blood vessel with a pulsed wave ultrasound beam; (c) receiving a n single dimension vector of complex Doppler shift frequency reflections along the ultrasound beam for a plurality of gates i = 1 to n therealong; (d) repeating steps (b) and (c) m times for obtaining a m x n two dimension matrix of energy associated values EJJ; (e) calculating a n single dimension vector of energy values Ej along the ultrasound beam; (f) determining the beam corrected chord length L of a portion of the ultrasound beam extending between the outermost surface So and the innermost surface Si of the blood vessel's sidewall correspondingly adjacent the ultrasound transducer, and remote therefrom; and (g) calculating the blood vessel diameter D according to the 5 relationship: D = L sin 0. 8. The method according to claim 7 wherein step (e) includes the steps of: (el) performing a Fast Fourier Transform operation on the m x n two l o dimension matrix of energy associated values EJJ; (e2) summing the energy values Ejj for each column j = 1 to m of the m x n two dimension matrix of energy associated values Ejj according to the relationship: ∑ E 'JjPR-ea'l 2 + E J "U I'~ma--ge- ' ; ^ (e3) repeating step (e2) for each gate i = 1 to n along the ultrasound 15 beam. 9. The method according to claim 7 wherein step (e) includes the steps of: (el) summing the energy values Ejj for each column j = 1 to m of the 0 m x n two dimension matrix of energy associated values Ejj according to the relationship: m i Σ E ,jReal 2 + E ιjlma B e 2 5 and J=l (e2) repeating step (el) for each gate i = 1 to n along the ultrasound beam. 25 10. The method according to claim 7 wherein step (e) includes the steps of: (el ) summing the real part or the imaginary part of the energy values E υ for each column j = 1 to m of the m x n two dimension matrix of energy associated values E,,; and (e2) repeating step (el) for each gate i = 1 to n along the ultrasound beam. 11. The method according to any one of claims 7 to 10 wherein step (f) includes the steps of (fl) determining a group size s of a group of consecutive gates (i, i+s) along the ultrasound beam, thereby specifying (n-s) groups of consecutive gates therealong; (f2) calculating the coefficients a, b and c of the equation y = a + bE, + cE, for (n-s) groups of consecutive gates (i, i+s) for i = l to (n-s); (β) calculating a leftmost boundary identification value Tι e ft according to the relationship: τ = c for each group of consecutive gates (i, i+s); (f4) determining the first group of consecutive gates along the ultrasound beam adjacent the ultrasound transducer with the maximum Tι ef t value of the (n-s) T| ef t values; (f5) selecting the first gate of the first group of consecutive gates closest to the ultrasound transducer as the gate which intercepts with the outermost surface So of the blood vessel's sidewall; (f6) repeating steps (f2) and (β) for (n-s) groups of consecutive gates for gates (i, i-s) for i = n to s for calculating a rightmost boundary identification value Tπght; (f7) determining the last group of consecutive gates along the ultrasound beam remote from the ultrasound transducer with the maximum Tπg ht value of the (n-s) T πg ht values; (f8) determining the last gate of the last group of consecutive gates furthermost from the ultrasound transducer as the gate which intercepts with the innermost surface Si of the blood vessel's sidewall; and (f9) determining the beam corrected chord length L from the first gate and the last gate. 12. The method according to any one of claims 7 to 10 wherein step (f) includes the steps of: (fl) determining the average absolute derivative threshold energy AADTE of the n single dimension vector of energy values E; according to the relationship: AADTE = - ∑ |E 1+ I - E , | (f2) determining the average amplitude threshold energy AATE of the n single dimension vector of energy values Ej according to the relationship: A . ^^ mean of E, values + median of E, values AATE = ! ! ; 2 (β) determining that the first gate along the ultrasound beam closest to the ultrasound transducer whose energy value Ej satisfies the conditions Ej > AADTE and Ej > AATE; (f4) determining the last gate along the ultrasound beam furthermost from the ultrasound transducer whose energy value Ej satisfies the conditions E, > AADTE and E, > AATE; and (f5) determining the beam corrected chord length L from the first gate and the last gate. 13. The method according to claim 12 further comprising the step (f6) of removing one or more pairs of phantom blood vessel borders intermediate the first gate and the last gate. 14. The method according to claim 13 wherein the step (f6) includes the steps of: (f61) generating a g single dimension vector K of all the gates i = 1 to n along the ultrasound beam whose energy value Ej satisfies the conditions Ei > AADTE and E; > AATE; (f62) generating a h single dimension vector DK where DK h = K h+ , - K h for h = l to g; (f63) calculating the parameter Average DK according to the relationship: AverageDK=-TDK h g w (f64) determining the leftmost region of gates which satisfies the condition DK h /2 > Average DK, and specifying that the leftmost gate of the leftmost region is the outermost surface So; and (f65) determining the rightmost region of gates which satisfies the condition DK h /2 > Average DK and specifying that the rightmost gate of the rightmost region is the innermost surface Sj. 15. The method according to any one of the claims 7 to 14 wherein step (g) includes determining the beam corrected chord length L according to the relationship: L = P - B/tan 0 where P is the measured chord length between the first gate and the last gate, and B is the beam width of the ultrasound beam. 16. The method according to any one of the claims 7 to 15 and further comprising the step (h) of calculating blood flow in the blood vessel as a function of its blood vessel diameter and blood flow velocity therein. 17. The method according to any one of the claims 7 to 16 and further comprising the step (i) of calculating the vascular elasticity of the blood vessel according to the relationship: D - D, D d where D s is the blood vessel diameter at peak systole and Dd is the blood vessel diameter at diastole. 18. The method according to any one of claims 7 to 17 and further comprising the steps of: (j l) determining the blood flow velocity profile across the diameter of the blood vessel; and (j2) calculating shear rate at the outermost surface So and the innermost surface Si of the blood vessel's sidewall relative to the ultrasound transducer according to the relationship: dV — at D =0,and D. dD 19. The method according to any one of claims 7 to 18 and further comprising the steps of: (kl ) measuring time dependent arterial blood pressure Pr(t); and (k2) calculating a time dependent distal resistance index Rs(t) according to the relationship: Rs(t) =^ F(t) where is F(t) is the instantaneous blood flow.

Inventors: BIBI RONI, LEVY ELI, MANOR DAN, BIBI, RONI, LEVY, ELI, MANOR, DAN
Applicants: BIBI RONI, BIOSONIX LTD, LEVY ELI, MANOR DAN, BIBI, RONI, BIOSONIX LTD., LEVY, ELI, MANOR, DAN
Application year: 1999
Main classification: A61B8
IPC codes: A61B8, G01S15