An ultrasonic imaging method for precise location or sizing of an object

Abstract

A method for characterizing an object using an ultrasonic probe, the method comprising the steps of: Carrying out several iterations of the steps of: Emitting (201) an ultrasonic field having an aperture of a given size, Measuring (202) an echo of the ultrasonic field after reflection on an area of ​​interest of an object to be imaged, At each new iteration, modifying (203) the size of the aperture of the ultrasonic field, For at least one point of interest in the area of ​​interest, recording (204), on the measurement of the echo, the associated time of flight, Determining (205), from said time of flight measurements, a model of variation of the times of flight as a function of the size of the aperture of the ultrasonic field, Extrapolating (206) the time of flight of the point of interest for an aperture size tending towards 0 from said model. Figure 2

Description

Title of the invention: Ultrasonic imaging method for the precise location or sizing of an object

[0001] The invention relates to the field of ultrasound imaging, in particular medical imaging, and relates to a method for improving the accuracy of such measurements when they are carried out using an ultrasound probe having an opening field of the emitted ultrasound field which has a given size.

[0002] The invention applies in particular to the imaging of blood vessels, for example arteries, with a view to precisely determining the diameter of such vessels, but it is not limited to this application and aims more generally at improving the measurement precision for the ultrasound imaging of all types of object in the medical field or the field of non-destructive testing by ultrasound.

[0003] Generally speaking, and particularly in the medical field, ultrasound imaging is a tool allowing the precise monitoring, sometimes in real time, of certain anatomical objects such as blood vessels. In particular, it allows the dimensions of these vessels to be located and measured. However, the accuracy of ultrasound measurements varies depending on the type of equipment used.

[0004] The development of ultrasound-based technologies makes it possible to have compact monitoring systems offering a non-invasive solution. Fully automated portable real-time monitoring makes it possible to provide both relevant information on daily life and data over longer periods of time, in situations that are inaccessible in care services with fixed devices.

[0005] However, portable ultrasound imaging devices are limited in resources and energy consumption, this imposes a compromise on the precision and frequencies used, which in turn limits the usability of the collected data. These limitations in frequency and precision make the discovery of diseases less early and limit the progress and understanding of phenomena of interest, for example cardiovascular diseases in the medical field. Conventionally, existing solutions tend to favor precision to the detriment of energy consumption, low cost and simplicity of algorithms.

[0006] There is therefore a general problem of improving the accuracy of ultrasound imaging systems without increasing their energy consumption, their cost, and without needing to modify existing equipment.

[0007] In the field of medical imaging, several existing methods make it possible to detect and characterize arteries. We can cite in particular references [1] and [2] as well as patent application WO2016057233.

[0008] All these methods have the disadvantage of suffering from limited measurement accuracy because they are most often based on an ultrasonic acquisition method that uses a set of elements to generate an ultrasonic field with an opening having a size that depends on the number of elements. The accuracy of the measurements depends on different parameters, in particular the frequency and the bandwidth of the signal. But it also depends on the size of the active window of the probe, that is to say the total size of the set of active elements.

[0009] The smaller the active window, the higher the measurement accuracy in terms of resolution. However, an active window that is too small has the disadvantage of lowering the signal-to-noise ratio because the signal amplitude is lower. It is for this second reason that ultrasonic probes are generally based on multi-element transducers that use several active elements to synthesize an ultrasonic beam in order to focus the beam by coherent summation of the amplitudes of the different elements.

[0010] The invention is based on an algorithmic solution that makes it possible to improve the resolution and precision of the measurement without modifying the acquisition equipment. The method is based on carrying out several successive measurements by varying the number of active elements or the aperture size of the generated ultrasonic field and then extrapolating the measurement that would have been obtained with an aperture close to zero from the different measurement points carried out.

[0011] The subject of the invention is a method for characterizing an object by means of an ultrasonic probe, the method comprising the steps of: - Carry out several iterations of the steps of: i. Emit an ultrasonic field having an aperture of a given size, ii. Measure an echo of the ultrasonic field after reflection on an area of ​​interest of an object to be imaged, iii. At each new iteration, modify the size of the ultrasound field opening, - For at least one point of interest in the area of ​​interest, note, on the echo measurement, the associated flight time, - Determine, from said flight time measurements, a model of variation of flight times as a function of the size of the opening of the ultrasound field, - Extrapolate the flight time of the point of interest for an opening size tending towards 0 from said model.

[0012] According to a particular aspect of the invention, the ultrasonic probe comprises a plurality of elements and the variation in the size of the opening of the ultrasonic field is obtained by varying the number of active receiving elements.

[0013] According to a particular aspect of the invention, the number of active reception elements is a multiple of two.

[0014] According to a particular aspect of the invention, the number of active elements in transmission is equal to the number of active elements in reception or to the maximum number of elements that the probe comprises.

[0015] According to a particular aspect of the invention, the object to be imaged is a blood vessel and the point of interest is a point on a wall of the blood vessel.

[0016] According to a particular aspect of the invention, the method is applied for two points of interest corresponding to a first point of the distal wall of the blood vessel and a second point of the proximal wall of the blood vessel, diametrically opposite the first point and the method further comprises an estimation of the diameter of the blood vessel from the extrapolated flight times of the two points.

[0017] The subject of the invention is an ultrasound imaging device comprising an ultrasound probe and a processing unit configured to carry out the steps of the method according to the invention.

[0018] The invention thus makes it possible to optimize the precision of the measurements without the need to modify the ultrasonic probe.

[0019] Other characteristics and advantages of the present invention will appear more clearly on reading the description which follows in relation to the following appended drawings.

[0020] [Fig.l] represents a diagram of an ultrasonic multi-element probe capable of carrying out an ultrasonic signal acquisition sequence to image a blood vessel,

[0021] [Fig.2] represents a flowchart of the steps of a method for measuring a signal ultrasound according to one embodiment of the invention,

[0022] [Fig.3a] represents an example of an ultrasound image obtained to characterize a blood vessel,

[0023] [Fig.3b] represents an ultrasonic signal extracted from a column of the image of the [Fig.3a],

[0024] [Fig.4a] represents a diagram of an ultrasonic probe according to a first confi active window size configuration in reception,

[0025] [Fig.4b] represents a diagram of an ultrasonic probe according to a second confi active window size configuration in reception,

[0026] [Fig.4c] represents a diagram of an ultrasonic probe according to a third confi active window size configuration in reception,

[0027] [Fig.5] represents an example of an ultrasonic signal obtained according to a configuration particular active window size,

[0028] [Fig.6a] represents a diagram giving the variation of the flight time of a first point of interest of the ultrasonic signal as a function of the active window size,

[0029] [Fig.6b] represents a diagram giving the variation of the flight time of a second point of interest of the ultrasound signal as a function of the active window size,

[0030] [Fig.6c] represents a diagram of a mathematical model of the variation of the estimated diameter of a blood vessel from the flight times of the two points of interest measured in Figures 6a and 6b,

[0031] The invention is now described in the context of application of medical imaging of a blood vessel, for example an artery. Although the invention applies advantageously to this example, it is not limited to this particular case and applies more generally for any type of object to be imaged, in particular in the field of non-destructive testing and for any point of interest of an object that one seeks to locate precisely.

[0032] [Fig.l] shows schematically an example of a multi-element ultrasound probe capable of imaging an area of ​​the human body using an ultrasound beam. In the example of [Fig.l], the area corresponds to a transverse plane of a blood vessel that one wishes to locate precisely or whose diameter one wishes to determine precisely.

[0033] In the example of [Fig.l], the probe 101 is positioned in contact with the skin 103 so that the row of elements 102 is located substantially in a transverse plane of an artery 104 to be imaged. The probe 101 is not necessarily centered on the artery 104, it is sufficient that the artery is covered in emission and reception by the ultrasound beam generated by the probe so as to obtain a transverse imprint of the artery.

[0034] To carry out an acquisition, the probe is positioned at a given point and a group of elements is activated in emission so as to generate an ultrasonic field in a given direction. The echoes of the field on the covered area are then measured by the same group of elements or a group of elements in limited number. In the example of [Fig.l], the ultrasonic field is emitted in a direction perpendicular to the axis of the alignment of the elements 102 which also corresponds locally to the plane of the skin 103 on which the probe 101 is positioned.

[0035] [Fig.3a] shows an example of a 2D image obtained by carrying out several successive acquisitions, each time shifting the emission center of the ultrasound field relative to the covered area.

[0036] [Fig.3b] shows a column of the 2D image of [Fig.3a] which corresponds to a signal measured for an acquisition corresponding to a position of the probe located directly above the center of the vessel to be imaged.

[0037] Indeed, the 2D image of [Fig.3a] corresponds to a matrix of which each column is one of the ultrasonic signals acquired by the probe for a given position of the emitted field relative to the imaged area.

[0038] In [Fig.3b], we have identified by two triangles, two extrema which correspond to the echoes of the ultrasound field on the distal and proximal walls of the blood vessel (in the occurrence of a radial artery).

[0039] These two points correspond to points of interest in the context of determining the diameter of the vessel. Indeed, from the measurement of the flight times of these two extrema, it is possible to deduce the positions of the two points and then the diameter by assuming that the signal corresponds to a path which passes through the center of the artery. The internal diameter of the vessel is equal to D=0.5C.(t2-ti), where t2, ti are the abscissas of the two extrema (flight times) and C the propagation speed of the ultrasonic wave in the medium, in this case the blood.

[0040] However, the accuracy of the measurement of the time of flight of a point of interest depends on the size of the active window of the transmitting probe as is now explained.

[0041] Figures 4a, 4b and 4c show three different acquisition configurations for the same ultrasound probe 401 arranged directly above a radial artery 402.

[0042] For the first configuration shown in [Fig.4a], the number of active elements 403 in transmission and reception is equal to 16. In other words, the ultrasonic field is generated from the 16 central elements of the probe and also measured by these 16 elements. This acquisition makes it possible to obtain a first measurement of the signal shown in [Fig.3b].

[0043] The second configuration shown schematically in [Fig.4b] shows a situation where the number of active elements 404 in reception is equal to 12. In this configuration, the number of active elements in transmission can also be taken equal to 12 or can be taken equal to 16, that is to say the maximum number of active elements in transmission predefined according to the intended application.

[0044] The third configuration shown in [Fig.4c] shows yet another situation where the number of active elements 405 in reception is equal to 8. The number of active elements in transmission is equal to 8 or 16.

[0045] Generally speaking, Figures 4a, 4b and 4c show that it is possible to perform the same measurement from a variable active window size. The larger the window size, the higher the signal-to-noise ratio, but the lower the measurement accuracy of the echo at a given point. Conversely, a minimum active window size is necessary to obtain a measurement with a usable signal-to-noise ratio.

[0046] With reference to [Fig.2], the measurement method according to the invention begins with steps 201, 202, 203 which consist of carrying out several successive acquisitions of the same ultrasonic signal (for the same position of the probe relative to the object to be imaged) by varying the size of the active window at each iteration.

[0047] For example, in the case of a multi-element transducer, the number of active receiving elements can be reduced at each iteration relative to the maximum number of elements used to generate the ultrasonic beam. At each iteration, the number of active elements in transmission can be left constant or the group of active elements in transmission can be taken equal to the group of active elements in reception.

[0048] For example, at each iteration, the number of active elements in reception can be reduced by a factor of 2.

[0049] According to another embodiment, if the ultrasound probe is manufactured using a technology which allows the opening of the ultrasound field to be varied with a single element, then the variation in the number of active receiving elements is replaced by a variation in the opening field at each iteration.

[0050] At the end of all the iterations of steps 201, 202, 203, N measurements of the same ultrasonic signal are obtained, with N the number of acquisitions carried out.

[0051] One or more points of interest are then identified on the acquired ultrasound signal. For example, for the case of the signal of [Fig.5], two points of interest 501,502 are identified which correspond to echoes of the signal on the internal distal and proximal walls of the blood vessel.

[0052] We wish to determine precisely, for each of these two points, the flight time or the associated depth (the two quantities being linked together by the speed of propagation of the ultrasonic wave in the medium located between the probe and the artery) which is represented on the abscissa of the diagram in [Fig.5].

[0053] For each point of interest considered, its abscissa is noted (expressed in time of flight or distance) and the diagrams shown in Figures 6a and 6b are plotted (in step 204), which give the evolution of these measurements as a function of the number of active elements in reception, also called the number of channels in Figures 6a and 6b. [Fig.6a] corresponds to the position of the echo of the signal on the proximal wall and [Fig.6b] corresponds to the position of the echo of the signal on the distal wall. In the examples illustrated, the number of channels varies from 8 to 28, but this example is not limiting. On the ordinate, the time of flight of each measurement is found.

[0054] In step 205, a numerical model of the evolution of the flight time variation curves as a function of the number of channels for each point of interest is then determined by mathematical optimization.

[0055] This mathematical model is for example determined by a model in the form of a second-degree polynomial function or any other suitable numerical model. It can be defined by means of an interpolation of the measured points of the curve. This interpolation can be carried out by means of a mixture of Gaussian functions or learned by a trained model of neural networks or any other suitable numerical optimization algorithm.

[0056] In [Fig.6c] an example of such a numerical model determined for the difference between the two curves of figures 6a and 6b which corresponds, in the intended application case, to the diameter of the blood vessel is shown.

[0057] The mathematical model can be determined for each curve associated with each point of interest or for the final quantity that one wishes to determine from several points of interest, in this case the difference between the two flight times.

[0058] Finally, in step 206, the mathematical model obtained is extrapolated to determine an asymptotic value for a number of channels tending towards 0. Indeed, this value corresponds to the most precise measurement in terms of resolution and its determination via an extrapolation of a model makes it possible not to be subject to the problem of low signal-to-noise ratio inherent in a measurement carried out with a very small active window.

[0059] The diameter of the vessel is for example determined using the following relation:

[0060] D=0.5(tdistai(0)- tproximai(0)).C, where C denotes the propagation speed of Fonde ul- trasonic in the crossed medium, tdistai(0) and tproximai(O) are the values ​​extrapolated for a number of channels tending towards 0 of the flight time evolution models associated with the points of interest corresponding to the echoes of the ultrasound field respectively on the distal wall and the proximal wall of the vessel.

[0061] Generally speaking, the invention can be applied identically to improve the precision of a time-of-flight measurement of a point of interest corresponding to the echo of an ultrasonic field on the surface of an object to be imaged. References

[0062] [1] JH Gagan et al., “Automated Segmentation of Common Carotid Artery in Ul- trasound Images," in IEEE Access, vol. 10, pp. 58419-58430, 2022

[0063] [2] “System A feasibility study of a PMUT-based wearable sensor for the automatic monitoring of carotid artery parameters”, 2021 IEEE International Ultrasonics Symposium (IUS)

Claims

Claims

1. A method of characterizing an object using an ultrasonic probe, the method comprising the steps of: - Performing several iterations of the steps of: i. Emitting (201) an ultrasonic field having an aperture of a given size, ii. Measuring (202) an echo of the ultrasonic field after reflection on an area of ​​interest of an object to be imaged, iii. At each new iteration, modify (203) the size of the opening of the ultrasound field, - For at least one point of interest in the area of ​​interest, note (204), on the measurement of the echo, the associated time of flight, - Determine (205), from said time of flight measurements, a model of variation of the times of flight as a function of the size of the opening of the ultrasound field, - Extrapolate (206) the time of flight of the point of interest for an opening size tending towards 0 from said model.

2. Method for characterizing an object according to claim 1 in which the ultrasonic probe (101) comprises a plurality of elements (102) and the variation of the size of the opening of the ultrasonic field is obtained by varying the number of active elements in reception.

3. Method of characterizing an object according to claim 2 in which the number of active receiving elements is a multiple of two.

4. Method for characterizing an object according to any one of claims 2 or 3 in which the number of active elements in transmission is equal to the number of active elements in reception or to the maximum number of elements that the probe comprises.

5. A method of characterizing an object according to any preceding claim wherein the object to be imaged is a blood vessel and the point of interest is a point on a wall of the blood vessel.

6. Method for characterizing an object according to claim 5 in which the method is applied for two points of interest corresponding to a first point of the distal wall of the blood vessel and

7. a second point on the proximal wall of the blood vessel, diametrically opposite the first point and the method further comprises estimating the diameter of the blood vessel from the extrapolated times of flight of the two points. An ultrasound imaging device comprising an ultrasound probe and a processing unit configured to perform the steps of the method according to any one of the preceding claims.

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