U.S. patent application number 11/123856 was filed with the patent office on 2005-11-17 for method and apparatus for improving the accuracy with which the speed of a fluid is measured.
Invention is credited to Hascoet, Gerard, Pechoux, Thierry.
Application Number | 20050256408 11/123856 |
Document ID | / |
Family ID | 9550922 |
Filed Date | 2005-11-17 |
United States Patent
Application |
20050256408 |
Kind Code |
A1 |
Hascoet, Gerard ; et
al. |
November 17, 2005 |
Method and apparatus for improving the accuracy with which the
speed of a fluid is measured
Abstract
The present invention relates to a method and associated
apparatus for improving the accuracy with which the speed of a
fluid, such as a liquid, in particular blood flowing in a duct,
such as a blood vessel, in particular the aorta, is measured by
means of a signal emitted by a Doppler transducer (4). In
characteristic manner, according to the method, the Doppler
transducer is associated with a programmable memory (50) which
contains at least one correction data item for correcting the
Doppler signal transmitted by the transducer (4) to a transducer
control and computer unit (8). Said computer unit (8) incorporates
said signal correction data item in its computation (at 16) of each
speed measurement on the basis of each signal emitted by the
Doppler transducer, and it computes the speed value while taking
account of said correction data item so as to provide a corrected
measurement of the speed of said fluid, thereby improving its
accuracy.
Inventors: |
Hascoet, Gerard; (Paris,
FR) ; Pechoux, Thierry; (Paris, FR) |
Correspondence
Address: |
AMSTER, ROTHSTEIN & EBENSTEIN LLP
90 PARK AVENUE
NEW YORK
NY
10016
US
|
Family ID: |
9550922 |
Appl. No.: |
11/123856 |
Filed: |
May 6, 2005 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11123856 |
May 6, 2005 |
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10340552 |
Jan 10, 2003 |
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6905469 |
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10340552 |
Jan 10, 2003 |
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09922603 |
Aug 3, 2001 |
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6506159 |
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09922603 |
Aug 3, 2001 |
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09522089 |
Mar 10, 2000 |
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6287260 |
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Current U.S.
Class: |
600/454 ;
600/455 |
Current CPC
Class: |
G01F 1/663 20130101;
G01F 1/667 20130101; A61B 8/06 20130101; G01P 5/241 20130101; G01S
15/58 20130101; A61B 8/12 20130101 |
Class at
Publication: |
600/454 ;
600/455 |
International
Class: |
A61B 008/02 |
Foreign Application Data
Date |
Code |
Application Number |
Oct 14, 1999 |
FR |
FR 99 12815 |
Claims
1-18. (canceled)
19. A method for measuring the speed of blood flowing in the aorta
by means of a signal emitted by a Doppler transducer and for
measuring the diameter of the aorta, the method comprising
inserting an intracorporeal probe into the esophagous of a subject,
wherein: (a) a Doppler transducer for measuring the speed of blood
flowing in the aorta and an ultrasound transducer for measuring the
diameter of the aorta are incorporated or integrated in the
intracorporeal probe, the Doppler transducer is mounted on the
probe to emit an ultrasound beam at an angle relative to the
longitudinal axis of the probe, and the probe comprises a
programmable memory; (b) the Doppler transducer is associated with
the programmable memory, wherein the programmable memory contains
at least one signal correction data item for correcting the Doppler
signal transmitted by the transducer to a transducer control and
computer unit; and (c) the computer unit incorporates the signal
correction data item in computing each speed measurement on the
basis of each signal emitted by the Doppler transducer, and
computes the speed value taking account of the signal correction
data item so as to provide a corrected measurement of the speed of
the blood.
20. The method of claim 19, wherein: (a) the programmable memory
also contains at least one sensitivity data item for informing the
user of a loss of sensitivity to the Doppler signal; (b) the
transducer control and computer unit verifies the sensitivity data
item present in the programmable memory on each measurement of the
signal transmitted by the transducer in order to verify that the
sensitivity actually obtained on the signal transmitted by the
transducer is not too far removed from the sensitivity value
present in the programmable memory; and (c) in the event of
sensitivity going beyond a specified limit value, the transducer
control and computer unit issues to the user a signal indicative of
a loss of sensitivity.
21. The method of claim 19, wherein the signal correction data item
is obtained from tests preferably performed at the manufacturing
site while performing preliminary use tests on the Doppler
transducer in order to verify the reliability of its signal.
22. The method of claim 20, wherein the sensitivity data item is
obtained during tests that are preferably performed at the
manufacturing site while measuring the flow speed of a fluid that
is flowing at a known speed.
23. The method of claim 19, wherein the signal correction data item
comprises at least the angle at which the Doppler beam is emitted
by the Doppler transducer relative to the axis of the probe, so
that the speed value takes account of the real working angle of the
beam from the Doppler transducer.
24. The method of claim 20, wherein the sensitivity data item
comprises at least one average of a plurality of sensitivity
measurements obtained over a corresponding number of uses of the
Doppler transducer, each sensitivity measurement resulting from the
amplitude of the signal received from the transducer.
25. The method of claim 20, wherein the transducer control and
computer unit continuously computes the mean of a plurality of
recently calculated sensitivity measurements and compares it with
the sensitivity mean initially entered as sensitivity data into the
programmable memory, and, beyond a certain difference relative to
the initially programmed sensitivity measurement, issues a signal
to the user indicative of a loss of sensitivity.
26. The method of claim 19, wherein at least one sensitivity data
item concerning the ultrasound transducer for measuring the
diameter of the aorta is provided in the programmable memory, so as
to verify its sensitivity over time, and likewise issue a signal to
the user in the event of a loss of sensitivity.
27. The method of claim 19, wherein the Doppler transducer is
mounted on the probe to emit an ultrasound beam at an angle of 60
degrees relative to the longitudinal axis of the probe.
28. An apparatus for measuring the speed of blood flowing in the
aorta by means of a signal emitted by a Doppler transducer and for
measuring the diameter of the aorta, said apparatus comprising a
Doppler transducer for measuring the speed of blood flowing in the
aorta, an ultrasound transducer for measuring the diameter of the
aorta, and a programmable memory containing at least one signal
correction data item for correcting the Doppler signal transmitted
by the Doppler transducer to a transducer control and computer
unit, wherein: (a) means are provided to enable the computer unit
to incorporate the signal correction data item in computing each
speed measurement on the basis of each signal emitted by the
Doppler transducer, and to compute the speed value taking account
of the signal correction data item so as to provide a corrected
measurement of the speed of the blood; and (b) the Doppler
transducer is incorporated or integrated in an intracorporeal probe
that can be inserted into the esophagus, and the Doppler transducer
is mounted on the probe to emit an ultrasound beam at an angle
relative to the longitudinal axis of the probe, and wherein the
probe also comprises the programmable memory connected to the
transducer control and computer unit, which memory is thus secured
to the probe and is dedicated thereto.
29. The apparatus of claim 28, wherein: (a) the programmable memory
also contains at least one sensitivity data item for informing the
user of a loss of sensitivity to the Doppler signal; (b) the
transducer control and computer unit verifies the sensitivity data
item present in the programmable memory on each measurement of the
signal transmitted by the transducer in order to verify that the
sensitivity actually obtained on the signal transmitted by the
transducer is not too far removed from the sensitivity value
present in the programmable memory; (c) signal-issuing means are
provided; and (d) in the event of sensitivity going beyond a
specified limit value, the transducer control and computer unit
issues a signal to the user, via the signal-issuing means, to
inform the user of a loss of sensitivity.
30. The apparatus of claim 28, wherein the programmable memory
contains a signal correction data item obtained from tests
preferably performed at the manufacturing site while performing
preliminary use tests on the Doppler transducer in order to verify
the reliability of its signal.
31. The apparatus of claim 29, wherein the programmable memory
contains a sensitivity data item obtained during tests that are
preferably performed at the manufacturing site while measuring the
flow speed of a fluid that is flowing at a known speed.
32. The apparatus of claim 28, wherein the signal correction data
item comprises at least the angle at which the Doppler beam is
emitted by the Doppler transducer relative to the axis of the
probe, so that the speed value takes account of the real working
angle of the beam from the Doppler transducer as actually created
on the probe.
33. The apparatus of claim 29, wherein the sensitivity data item
comprises at least one average of a plurality of sensitivity
measurements obtained over a corresponding number of uses of the
Doppler transducer, each sensitivity measurement resulting from the
amplitude of the signal received from the transducer.
34. The apparatus of claim 29, wherein the transducer control and
computer unit continuously computes the mean of a plurality of
recently calculated sensitivity measurements and compares it with
the sensitivity mean initially entered as sensitivity data into the
programmable memory, and, beyond a certain difference relative to
the initially programmed sensitivity measurement, issues a signal
to the user, via the signal-issuing means, to indicate a loss of
sensitivity.
35. The apparatus of claim 28, wherein the programmable memory
contains at least one sensitivity data item concerning the
ultrasound transducer for measuring the diameter of the aorta, so
as to verify its sensitivity over time, and likewise issue, via a
signal-issuing means, a signal to the user in the event of a loss
of sensitivity.
36. The apparatus of claim 28, wherein the Doppler transducer is
mounted on the probe to emit an ultrasound beam at an angle of 60
degrees relative to the longitudinal axis of the probe.
Description
[0001] The present invention relates essentially to a method and to
apparatus for improving the accuracy with which the speed of a
fluid, such as a liquid, in particular blood flowing in a duct,
such as a blood vessel, in particular the aorta, is measured by
means of a signal emitted by a Doppler transducer.
BACKGROUND OF THE INVENTION
[0002] Document FR-A-2 424 733 INSERM discloses an ultrasound
intracorporeal probe that is inserted into the esophagus to measure
the flow rate in the aorta. That prior probe is characterized by a
catheter structure whose distal portion has a bag that can be
inflated from the outside with a liquid and that surrounds the
ultrasound emitter which is housed entirely inside the bag which
serves to prevent the emitter from moving inside the duct and which
serves to couple the emitter acoustically. The emitter is mounted
to rotate inside said inflatable bag on a support block which is
disposed substantially on the longitudinal axis of the probe, and
it is rotated by a flexible cable connected at its proximal end at
the outside to rotary drive means, e.g. in the form of a knob (see
the claims and the corresponding text describing the figures, in
particular page 2, line 24 to page 4, line 29).
[0003] That prior INSERM document has been improved in the context
of document U.S. Pat. No. 5,479,928 according to which the
intracorporeal probe has in combination: at least one broad-beam
ultrasound transducer fixed on the support block in such a manner
as to be oriented at an angle of inclination that is not
perpendicular relative to the longitudinal axis of the probe; and
at least one narrow beam ultrasound transducer fixed on the support
block so as to be oriented at an angle that is essentially
perpendicular relative to the longitudinal axis of the probe so as
to be oriented substantially perpendicularly relative to the
longitudinal axis of a duct in which the speed of a liquid is to be
measured, and in particular the flow rate of the liquid,
specifically the flow rate of blood when the duct is a blood
vessel.
[0004] The improvement according to that document is entirely
satisfactory and is available on the market from SOMETEC under the
trade name DYNEMO 3000.RTM..
OBJECTS AND SUMMARY OF THE INVENTION
[0005] A main object of the present invention is to resolve the
novel technical problem consisting in supplying a solution enabling
account to be taken of each feature of the Doppler transducer in
order to improve the accuracy with which the speed of a fluid, such
as a liquid, is measured by means of a signal emitted by such a
Doppler transducer.
[0006] Another main object of the present invention is to supply a
solution making it possible also to take account of the 3D position
of a Doppler transducer, and in particular the angle at which it
emits the ultrasound beam, thereby improving the accuracy with
which the speed of a fluid, such as a liquid, is measured by means
of the signal emitted by such a Doppler transducer.
[0007] Another main object of the present invention is to resolve
the said novel technical problems in a manner that is particularly
simple, low cost, reliable, and usable on a medical and industrial
scale.
[0008] Those problems are resolved for the first time by the
present invention at low manufacturing cost by means of a design
that is particularly simple, using a small number of parts, while
conserving the operating advantages of prior art probes, in
particular the improved probe constituting the subject matter of
document U.S. Pat. No. 5,479,928, and sold in the form of the
DYNEMO 3000.RTM. appliance.
[0009] In a first aspect, the present invention provides a method
of improving the accuracy with which the speed of a fluid, such as
a liquid, in particular blood flowing in a duct, such as a blood
vessel, in particular the aorta, is measured by means of a signal
emitted by a Doppler transducer, the method being characterized in
that the Doppler transducer is associated with a programmable
memory which contains at least one correction data item for
correcting the Doppler signal transmitted by the transducer to a
transducer control and computer unit, in that said computer unit
incorporates said signal correction data item in its computation
during each speed measurement on the basis of each signal emitted
by the Doppler transducer, and computes the speed value while
taking account of said correction data item, so as to provide a
corrected measurement of the speed of said fluid, thereby improving
the accuracy of the measurement.
[0010] According to an advantageous characteristic of the method,
it is characterized in that said Doppler transducer is incorporated
or integrated in a probe, in particular an intracorporeal Doppler
effect probe, said Doppler transducer being mounted on the probe to
emit an ultrasound beam at an angle relative to the longitudinal
axis of the probe; and in that said probe also comprises said
programmable memory.
[0011] According to another advantageous implementation of the
method, it is characterized in that said programmable memory also
contains at least one sensitivity data item for informing the user
of loss of sensitivity to the Doppler signal, and in that said
transducer control and computer unit verifies said sensitivity data
item present in the programmable memory on each measurement of the
signal transmitted by the transducer in order to verify that the
sensitivity as actually obtained on a signal transmitted by the
transducer is not too far removed from the sensitivity value
present in the programmable memory, and on going beyond a specified
limit value, said transducer control and computer unit issues a
signal to the user indicative of a loss of sensitivity.
[0012] According to yet another advantageous characteristic of the
invention, the method is characterized in that the said signal
correction data item is obtained on the basis of tests, preferably
performed at the manufacturing site, while performing preliminary
use tests on the Doppler transducer in order to verify the
reliability of its signal.
[0013] According to another advantageous characteristic of the
method of the invention, it is characterized in that the
sensitivity data item is obtained during tests, preferably
performed at the manufacturing site, while measuring the flow speed
of a fluid that is flowing at a known speed.
[0014] According to yet another advantageous characteristic of the
method of the invention, the method is characterized in that the
signal correction data item comprises at least the angle at which
the Doppler beam is emitted by the Doppler transducer relative to
the axis of the probe, so that the speed value takes account of
said real working angle of the beam from the Doppler
transducer.
[0015] Advantageously, the sensitivity data comprises at least one
average of a plurality of sensitivity measurements obtained with a
corresponding number of uses of the Doppler transducer, each
sensitivity measurement resulting from the amplitude of the signal
received from the transducer.
[0016] According to another advantageous characteristic of the
method of the invention, it is characterized in that the transducer
control and computer unit continuously computes the mean of a
plurality of recently calculated sensitivity measurements and
compares it with the sensitivity mean initially written as
sensitivity data in the programmable memory, and, beyond a certain
difference relative to the initially programmed sensitivity
measurement, issues a signal to the user indicative of a loss of
sensitivity.
[0017] According to yet another advantageous characteristic of the
invention, the method is characterized in that when the Doppler
transducer operates in combination with an additional transducer,
e.g. for measuring the diameter of a duct in which said fluid
flows, at least one sensitivity data item relating to said
additional transducer is preferably also provided in said
programmable memory in order to verify its sensitivity over time
and likewise issue a signal to the user in the event of sensitivity
being lost.
[0018] In a second aspect, the present invention also provides an
apparatus for improving the accuracy with which the speed of a
fluid, such as a liquid, in particular blood flowing in a duct,
such as a blood vessel, in particular the aorta, is measured by
means of a signal emitted by a Doppler transducer, the apparatus
being characterized in that it comprises a programmable memory
containing at least one correction data item for correcting the
Doppler signal transmitted by the transducer to a transducer
control and computer unit, and in that means are provided to enable
the computer unit to incorporate said signal correction data item
in computing each speed measurement on the basis of each signal
emitted by the Doppler transducer and to compute the speed value
taking account of said correction data item so as to provide a
corrected measurement of the speed of said fluid, thereby
increasing its accuracy.
[0019] In an advantageous embodiment, said Doppler transducer is
incorporated or integrated in a probe, in particular in a Doppler
effect intracorporeal probe, said Doppler transducer being mounted
on the probe to emit its ultrasound beam at an angle relative to
the longitudinal axis of the probe; and said probe also comprises
said programmable memory connected to said control and computer
unit, which memory is thus secured to the probe and is dedicated
thereto.
[0020] In another advantageous embodiment of the invention, said
programmable memory also contains at least one sensitivity data
item for informing the user of a loss of sensitivity in the Doppler
signal, and the transducer control and computer unit verifies said
sensitivity data item present in the programmable memory on each
measurement of the signal transmitted by the transducer in order to
verify that the sensitivity actually obtained on the signal
transmitted by the transducer is not too far removed from the
sensitivity value present in the programmable memory;
signal-issuing means are provided; and in the event of sensitivity
going beyond a set limit value, the transducer control and computer
unit issues a signal to the user via said signal-issuing means to
inform the user of a loss of sensitivity.
[0021] In another advantageous embodiment of the invention, said
signal correction data item is obtained from tests preferably
performed at the manufacturing site while performing preliminary
use tests on the Doppler transducer in order to verify the
reliability of its signal.
[0022] According to another advantageous characteristic of the
invention, the sensitivity data item is obtained during tests that
are preferably performed at the manufacturing site while measuring
the flow speed of a fluid that is flowing at a known speed.
[0023] According to another advantageous characteristic, the signal
correction data item comprises at least the angle at which the
Doppler beam is emitted by the Doppler transducer relative to the
axis of the probe, so that the speed value takes account of said
real working angle of the beam from the Doppler transducer as
actually mounted on the probe.
[0024] According to another advantageous characteristic of the
invention, the sensitivity data item comprises at least an average
of a plurality of sensitivity measurements obtained over a
corresponding number of uses of the Doppler transducer, each
sensitivity measurement resulting from the amplitude of the signal
received from the transducer.
[0025] According to another advantageous characteristic of the
invention, the transducer control and computer unit continuously
computes the mean of a plurality of recently calculated sensitivity
measurements and compares it with the sensitivity mean initially
entered as sensitivity data into the programmable memory and beyond
a certain difference relative to the initially programmed
sensitivity measurement, issues a signal to the user via said
signal-issuing means to indicate a loss of sensitivity.
[0026] According to another advantageous characteristic of the
invention, said apparatus further comprises an additional
transducer operating in combination with the Doppler transducer,
said additional transducer being intended, for example, to measure
the diameter of a duct in which said fluid flows, said programmable
memory preferably further containing at least one sensitivity data
item concerning said additional transducer so as to verify its
sensitivity over time and likewise issue, via said signal-issuing
means, a signal to the user in the event of a loss of
sensitivity.
[0027] It will thus be understood that by means of the invention
all of the previously-mentioned advantages are obtained.
BRIEF DESCRIPTION OF THE DRAWINGS
[0028] Other objects, characteristics, and advantages of the
invention appear clearly from a presently preferred embodiment of
the invention given merely by way of example and which does not
limit the scope of the invention in any way. In the drawings:
[0029] FIG. 1 shows a probe comprising a Doppler transducer in
accordance with FIG. 1 of U.S. Pat. No. 5,479,928, but modified to
incorporate a programmable memory in accordance with the present
invention, the probe being shown in cross-section and in elevation,
and, as in FIG. 1 of U.S. Pat. No. 5,479,928, in its working
position in the esophagus facing a blood vessel, in this case the
aorta 10;
[0030] FIG. 2 is a diagram showing the operation of calibrating the
FIG. 1 probe including the programmable memory in accordance with
the invention so as to determine the characteristic of the Doppler
transducer actually mounted on the probe; and
[0031] FIG. 3 is a calibration curve obtained during tests
performed at the manufacturing site to calibrate the Doppler
transducer 4 using the equipment of FIG. 2.
PREFERRED EMBODIMENT OF THE INVENTION
[0032] FIG. 1 reproduces FIG. 1 of U.S. Pat. No. 5,479,928=FR-A-2
695 999=EP-A-0 595 666 and uses essentially the same reference
numerals. With reference to FIG. 1, a catheter-shaped probe 1 for
measuring the speed of flow of a fluid F is manufactured in
conventional manner. For example, the probe is preferably intended
to measure the speed of flow of blood in the aorta 10, with the
probe 1 comprising a Doppler transducer 4 having a broad beam 4a
and being, by way of example, of the same type as that described in
U.S. Pat. No. 5,479,928=FR-A-2 695 999=EP-A-0 595 666, to which the
person skilled in the art can refer.
[0033] In this preferred embodiment, the Doppler transducer 4 is
designed on manufacture to present an angle of inclination for its
ultrasound beam of 60.degree. relative to the longitudinal axis
x-x' of the probe 1.
[0034] Incidentally, and preferably, the Doppler transducer 4
operates in combination with an additional transducer 5, for
example and preferably in the context of measuring the flow speed
of blood in a blood vessel, in this case the aorta 10, a transducer
which produces a narrow beam 5a as described in document U.S. Pat.
No. 5,479,928, with the transducer being placed parallel-to the
longitudinal axis of the probe so that its ultrasound beam extends
perpendicularly to the longitudinal axis of the probe for the
purpose of measuring the diameter and thus the flow section S of
the duct 10 in which there flows the fluid F whose speed is to be
measured, as described in the above-specified documents and as is
also known to the person skilled in the art, in particular from
those documents.
[0035] The other references in FIG. 1 which are identical to those
of FIG. 1 in U.S. Pat. No. 5,479,928=FR-A-2 695 999=EP-A-0 595 666
have the following meanings: reference numeral 1 represents the
outside portion of the catheter-shaped probe which, when installed
in a duct, in this case the esophagus 13 facing a blood vessel, in
this case the aorta 10, will take up a position that is fixed once
the inflatable balloon 6 has been inflated in the manner known to
the person skilled in the art.
[0036] The catheter-forming probe 1 has an internal flexible cable
2 connected at one of its ends to the support block 3 on which the
ultrasound transducers 4 and 5 are mounted. The transducers 4 and 5
are connected to an electric cable 7 placed in the probe 1 at its
distal end and leaving the probe 1 on the outside for connection to
a computer center or unit for controlling the transducers and for
processing the signals they deliver. The external end of the
flexible cable 2, remote from its end connected to the support
block 3, is connected to a drive member 9, in this case modified in
accordance with the present invention to be in the form of a handle
suitable for being taken hold of to rotate the flexible cable 2
appropriately about its own axis so as to rotate the support block
3, thereby directly turning the ultrasound beams 4a and 5a
respectively of the transducers 4 and 5 appropriately relative to
the duct 10 such as the aorta in which it is desired to measure the
flow speed of the fluid F, in this case blood. The control and
computer unit 8 comprises, as described in U.S. Pat. No. 5,479,928
and its equivalents, means 14 connected to the transducer 5 by a
link 7.sub.1 designed to determine the amplitudes of echo signals
received by the narrow beam transducer 5. These determination means
14 are connected to means 15 designed to detect the amplitude
maxima in the reflected signals.
[0037] Means 16 are also provided in the control and computer unit
8 to determine the range P.sub.2-P.sub.1 circumscribing the section
of the duct 10 at two opposite extreme points by taking account
solely of the echoes of the transducer 5 coming from said range
P.sub.2-P.sub.1. The means 16 are connected to the means 15 in
order to determine the range d.sub.2-d.sub.1 which corresponds to
the two extreme points of the duct, in this case the aorta 10, as
detected by the amplitude maxima in the reflected echoes of the
signals from the transducer 5. By knowing the range
d.sub.2-d.sub.1, it is possible to calculate the flow section S
since it is conventional to consider the duct 10, in this case the
aorta, to be circular in section. The means 16 which conventionally
comprise a microcomputer with appropriate software also takes
account of the angle of inclination .theta. between the two beams
4a and 5a as shown in FIG. 1 and as known, in particular by
construction. These means 16 control selection means 17 connected
to the transducer 4 by a link 7.sub.2. The means 17 make it
possible to select only those echoes of signals from the transducer
4 which are obtained over a response time interval corresponding to
the range P.sub.2-P.sub.1. The selection means 17 are connected to
conventional signal processing means 19 for obtaining a Doppler
signal. These processing means 19 are also connected to
conventional means 20 suitable for determining the mean speed
V.sub.m of the fluid F, in this case blood, as averaged over the
section S of the duct 10, in this case the aorta.
[0038] As described in U.S. Pat. No. 5,479,928, the unit 8 also has
means 21 suitable for measuring the energy backscattered by moving
particles, in this case red corpuscles in the blood. The output
from the measuring means 21 is connected to means 22 designed to
allow backscattered energy to pass through at one or more defined
instants, in particular during systole when measuring blood speed,
said means 22 also being connected to means 23 suitable for
determining those defined instants, and in particular the instant
at which systole occurs when blood is being measured. The means 22
deliver the value of the backscattered energy E.sub.S during
systole when measuring blood.
[0039] As described in U.S. Pat. No. 5,479,928, outside systole and
in particular during diastole, the area S.sub.D covered by the
particles actually in motion is likely to be smaller than the full
section S.
[0040] By taking account of backscattered energy during systole
E.sub.S and during diastole E.sub.D it is possible to determine the
real flow section or the effective ideal section S.sub.D involved
in the flow rate. This area is defined by the following
mathematical equation:
S.sub.D=S.(E.sub.D/E.sub.S)=S.K
[0041] The correction factor K is determined by correction means 24
connected to the means 21 and 22. The correction means 24 weight
the factor K by an empirical correction factor which takes account
of the technical characteristics of the transducer 4 in use and of
the means 19, in particular the minimum value of the speeds
detected and the passband of the emitted Doppler signal. The
correction means 24 are connected to means 25 that are also
connected to the means 20 for determining the mean speed over the
section. The means 25 make it possible to calculate a corrected
mean speed V.sub.C using the values for the mean speed over the
area and the correction factor K, and thus to calculate the flow
rate of the fluid F, in this case blood, moving through the
localized area S.sub.D, given knowledge of the section S of the
duct 10, in this case the aorta, as measured from distances D.sub.1
and D.sub.2 obtained by the transducer 5 disposed perpendicular to
the duct 10.
[0042] In an embodiment, the correction factor K can be represented
by the following equation: 1 K = ( E D E S ) n .times. k
[0043] in which:
[0044] K=correction factor;
[0045] E.sub.D=partial backscattered energy as defined above;
[0046] E.sub.S=total backscattered energy as defined above;
[0047] n is a number constituting another corrector factor; and
[0048] k is a correction factor as defined above depending on the
technical characteristics of the Doppler transducer 4 and of the
means that emit, receive, measure, and process the signals
associated with the Doppler effect transducer 4, including the
measurement means 19.
[0049] In the context of the present invention, in order to improve
the accuracy with which the speed of the fluid is measured,
provision is made for the apparatus that comprises the probe 1 and
its control and computer unit 8 to further comprise, in accordance
with the present invention, a programmable memory 50 which is
associated with the Doppler transducer 4 and which contains at
least one data item for correcting the Doppler signal transmitted
from the transducer 4 to the transducer control and computer unit
8, and in particular to its computation means 16. Such programmable
memories are commercially available, e.g. memories known as EEPROMs
or memories known as flash memories. The computation means 16
conventionally comprise, for example, a computer or a microcomputer
having appropriate software for controlling it. In this context,
the computation means 16 also has software incorporating said
signal correction data item as recorded in the programmable memory
50 each time it performs computations on each speed measurement as
obtained by means of the Doppler transducer 4.
[0050] According to a preferred characteristic of the invention,
this signal correction data item comprises at least the angle
.theta. at which the ultrasound beam is emitted by the Doppler
transducer 4. This angle is determined by performing a plurality of
speed measurements using the Doppler transducer 4 on a fluid that
is flowing along a calibrated duct of known diameter at a known
speed of fluid flow which is preferably adjusted to a different
known speed value for each measurement.
[0051] As is well known to the person skilled in the art, the flow
speed of the fluid as obtained by the Doppler effect is derived
from the mathematical equation: 2 V F F emit .times. C 2 Cos (
)
[0052] in which:
[0053] .DELTA.F=the frequency difference between reception and
emission, as a result of the Doppler effect;
[0054] F.sub.emit=the frequency at which the ultrasound beam is
emitted by the Doppler transducer;
[0055] C=the speed of propagation of sound in the medium, e.g. in
blood, equal to 1584 meters per second (m/s); and
[0056] .theta.=the angle at which the ultrasound beam is emitted by
the Doppler transducer 4 relative to the longitudinal axis x-x' of
the probe 1.
[0057] As a result, starting from the speed value as actually
measured and starting from an average of a plurality of speed
measurements at different flow speeds, the exact value of the angle
at which the ultrasound beam is emitted by the Doppler transducer
is obtained, i.e. as emitted by the probe.
[0058] This angle .theta. is thus incorporated in the programmable
memory 50 for subsequent use by the computer unit 8 in calculating
the real speed when measuring the speed of a fluid F flowing along
a given duct 10, in particular and preferably the aorta.
Preferably, the programmable memory is incorporated in or forms an
integral portion of the probe 1, thus having the advantage of
constituting a "signature" for the probe.
[0059] According to another advantageous characteristics of the
invention, the programmable memory 50 also includes data concerning
the sensitivity of the Doppler transducer 4.
[0060] This sensitivity data is obtained by programming the
transducer control and computer unit 8 which, on each speed
measurement, memorizes the amplitude of the signal received by the
transducer after a Doppler emission, and takes an average over a
plurality of measurements to calculate a reference sensitivity
which is subsequently stored by the computer unit 8 in the
programmable memory 50 and which is subsequently used as an initial
reference sensitivity, the control and computer unit 8 subsequently
and on each measurement recalculating the sensitivity of the
Doppler transducer 4 and preferably also taking an average over a
plurality of measurements, which it compares with the initial
sensitivity, such that in the event of too great a difference, e.g.
greater than .+-.10% relative to the initial sensitivity
measurement, the control and computer unit 8 issues a signal to the
user to inform the user that there has been a loss of sensitivity.
By way of example, this signal can be an alarm, or a warning lamp,
or a message.
[0061] For example, it is possible to use the rms value of the
received electrical signal. By way of example, this value is about
50 .mu.V for a conventional Doppler transducer 4 having dimensions
of 3 mm.times.4 mm and operating at about 5 MHz.
[0062] When an additional transducer 5 is used, in particular and
preferably for measuring the diameter of the duct 10 in which the
fluid F is flowing, the sensitivity of the additional transducer 5
is measured in the same manner, and this sensitivity measurement is
also put into the programmable memory 50 so as to be able to give
the user a similar signal concerning loss of sensitivity for this
additional transducer, when appropriate. By way of example, the
initial sensitivity value may be 80 .mu.V for an additional
transducer 5 having a diameter of 3 mm and operating at a frequency
of about 10 MHz.
[0063] It will thus be understood that the invention makes it
possible to monitor proper operation of the Doppler transducer 4
and possibly also of the additional transducer 5 effectively and to
inform the user, or to monitor any other additional transducer that
may be present on the probe.
[0064] In the context of the invention, any commercially available
programmable memory can be used. Examples of programmable memories
that are presently commercially available are electrically erasable
programmable random memories (EEPROMs) or indeed flash memories,
and the invention can be used with any other programmable memory
that may become available in the future.
[0065] With reference to FIG. 2, there is shown a diagram
representing the operation of calibrating the FIG. 1 probe
incorporating the programmable memory of the invention for the
purpose of determining the characteristics of the Doppler
transducer actually mounted in the probe, which characteristics are
subsequently used for correcting the measured flow speed of the
fluid F circulating in the duct 10. For this purpose, a tank 60 is
provided that is filled with a liquid, such as water, and that has
a well 60a which is filled with water and in which the active end
of the probe 1 having the said transducers 4 and 5 is inserted. The
well 60a thus symbolizes the esophagus 13 of a human body. The tank
60 has immersed therein a closed circuit 62 for circulating a fluid
63, such as water containing starch, so that the closed circuit 62
symbolizes the aorta 10 in which blood is flowing, and the flow
section S1 of the closed circuit 61 is calibrated, e.g. to a value
S.sub.1 that is close to the flow section S of the blood vessel, so
as to enable tests to be performed under conditions that are close
to the genuine working conditions of the probe 1 when in the human
body. The speed at which the liquid 63 flows round the closed
circuit 62 is determined by acting on a pump or any other similar
device for adjusting the flow speed of the liquid 63 in the closed
circuit 62. The flow speed of said fluid is read by any appropriate
flow measuring apparatus represented by 66. During these tests at
its manufacturing site, the probe is connected to the control unit
8 which contains in particular the computation means 16 such as a
computer or a microcomputer. A screen 68 is generally also provided
on which various parameters are displayed together with the results
obtained.
[0066] The tests performed comprise fixing the flow speed of the
liquid 63 round the closed circuit 62 at various different values
by means of the flow meter or spinner 64, thus making it possible
to plot a calibration curve for the Doppler transducer 4.
[0067] An example of such a calibration curve is given in FIG.
3.
[0068] In FIG. 3:
[0069] the ordinate (reference flow rate) corresponds to reference
measurements as provided by the flow rate measuring apparatus 66
(FIG. 2); and
[0070] the abscissa (measured flow rate) corresponds to the
measurements performed by means of the probe, assuming that the
ultrasound beam is inclined at an angle .theta. of 60.degree.
(.theta..sub.ideal=60.degree.) and using the computation means 16
(FIG. 2) of the probe control and computer unit 8 (FIG. 2).
[0071] The curve and the estimated angle and linear regression
correlation relating to the ultrasound beam are displayed on the
screen 68 (FIG. 2).
[0072] The control unit 8 (FIG. 2) automatically saves the
estimated angle (59.67.degree. in this example) for the ultrasound
beam in the memory of the probe 50 (FIG. 2).
[0073] From the equation mentioned above: 3 V F F emit .times. C 2
Cos ( )
[0074] it can be shown that: 4 est . = ArcCos ( reference flow rate
measured flow rate .times. Cos ( ideal ) )
[0075] The ratio 5 reference flow rate measured flow rate
[0076] is obtained directly by the slope of the regression line
through the points in FIG. 3.
* * * * *