Patent Application
20090074267
This application claims priority to European Patent Application No. EP 07116539.3, filed Sep. 17, 2007, entitled “METHOD FOR GENERATING QUANTITATIVE IMAGES OF THE FLOW POTENTIAL OF A REGION UNDER INVESTIGATION”. This reference is expressly incorporated by reference herein, in its entirety.
The present invention relates to a method for generating images of a region under investigation where the image information is related to the capability of such region to allow the flow of a fluid.
It is generally known that the capability of non-rigid pipes or conduits to allow a fluid to pass through can be determined by measuring the flow when the fluid is in a steady state condition and during transient state when the fluid is forced to flow at an increased rate. The differential value thus obtained is an indirect evaluation of the capability of the conduits to deform to comply with an increased demand of fluid flow. This differential approach has however several major drawbacks which are mainly due to the fact that it consists of single local measurements that are not informative of the spatial distribution of flow in a region under analysis, but only of the capability (reserve) that single conduits have to increase the flow. When structures having a large number of small conduits or permeable bodies have to be analysed, such methodology requires a distinct differential analysis for each of the flow patterns that can be identified which is a rather complex if not impracticable task for very complex structures.
In the medical field this approach is used in the so-called Coronary Flow Reserve (CFR) where the ability of coronary vessels to increase the blood flow during a stress test is measured.
Coronary arteries are vessels that transport oxygenated blood and nutrients to the heart supplying so the substrates required for the myocardial contraction. When a coronary artery has a critical obstruction it becomes unable to deliver the proper amount of oxygen and nutrients to the interested region causing ischemia. A complete coronary obstruction is the pathological basis of myocardial infarction.
Even relevant coronary obstruction (generally up to 75%) may be asymptomatic at rest and sometimes are difficult to detect in the clinical practice. In such clinical conditions, an increase of myocardial oxygen request, exceeding a particular threshold (Coronary Flow Reserve), e.g. during physical exercise or other stressing condition, may give rise to myocardial ischemia or necrosis.
CFR is usually calculated as the ratio between maximal (stress, hyperemic) to resting coronary blood flow. Stress is obtained by injection of a vasodilator drug such as adenosine or dypiridamole or by physical exercise to achieve the maximal dilation of microcirculation. Coronary flow velocities, at rest and peak of stress, are measured by means of pulsed Doppler technique directly on the coronary vessel visualized during an echocardiographic exam. The ratio between the value of flow velocity at stress and at rest is the CFR. For details see for example Dimitrow P P, Galderisi M, Rigo F. The non-invasive documentation of coronary microcirculation impairment: role of transthoracic echocardiography. Cardiovascular Ultrasound, 2005; 3:18-26.
The diagnosis of non-limiting flow coronary lesion is still a challenge in the clinical practice. In most instances it is based on the anatomical measurement of the effective degree of stenosis by means of invasive methods (like angiography or intravascular ultrasound). The invasive methods are still quite expensive, are available only in largest medical centers and, even now, imply a little but actual risk of serious complications. Non invasive methods of nuclear medicine (like SPECT or PET) are expensive too, require the administration of radioactive isotopes and have a limited repeatability. To further complicate the question, other ischemic conditions are associated with a damage of the smaller myocardial vessels (microcirculation) sometimes without any evidence of critical stenosis of the large epicardial coronaries (X syndrome). In these cases, being unable to visualize the microcirculation, also the invasive methods fail to detect the pathological condition.
CFR is an important functional parameter to understand the pathophysiology of coronary circulation especially because it can be evaluated in a non-invasive manner without requiring catheterisation as, for example, in angiography and more in general in the methods disclosed in Tobis J, Azarbal B, Slavin L. Assessment of Intermediate Severity Coronary Lesions in the Catheterization Laboratory. J Am Coll Cardiol 2007; 49:839-848.
However CFR, being a local differential analysis, cannot determine a real estimate of the actual flow of the microcirculation of the myocardium. CFR is, in fact, only a measure of the global capacity of flow in the coronaries well upstream the myocardial region. This results in a non accurate evaluation of a necrosis due for example to stroke. In fact it may happen in the so-called no-reflow status that a stenosis in a coronary artery determines a necrosis of the micro-circulation in a zone of the myocardium. Such stenosis causes a global reduction of the capacity of flow of the coronary which can be identified by CFR. However, once such stenosis is removed, for example by using a stent or with angioplasty, the flow in the diseased artery becomes normal again and CFR cannot help evaluate if the micro-circulation is irremediably compromised and if such zone of the myocardium is no longer able to react to an increased demand for blood flow under stress as no information of the spatial distribution of blood flow in the myocardial microcirculation can be determined with CFR. Furthermore not all the coronary vessels are easily visible during a standard echo examination and not in all patients is possible to see the coronary flow with colour Doppler thus limiting the application of CFR analysis only to those coronaries that can be reached in a trans-thoracic projection, namely the left anterior descending coronary artery and the right coronary artery
It is thus an object of the present invention to provide for a method for determining in an easy and effective way the capability of a body or an area to respond to a variation of flow demand.
Perfusion, that corresponds to the physical phenomenon commonly called filtration, represents the flow of a fluid into a porous or permeable medium. An example may be the diffusion of a polluting agent through the soil or more in general the passage of a fluid through a filtering medium also called percolation or infiltration. In the medical and/or veterinary field the term perfusion is generally used to identify the blood flow into a micro vascular tree.
In cardiology practice, the ability to evaluate, in a quantitative way, the myocardial perfusion, is of primary importance. In other branches of medicine perfusion is measured in kidney, liver, or other parenchymal organs to assess proper perfusion, lack of perfusion (necrotic region), or anomalous pattern of perfusion (cancer). For a reference see, for example, Becher H., Burns P N. Handbook of Contrast Echocardiography 2000 Springer-Verlag. ISBN 3-540-67083, Gibson C M, Cannon C P, Murphy S A, Marble S J, Barron H V, Braunwald E. Relationship of the TIMI Myocardial Perfusion Grades, Flow Grades, Frame Count, and Percutaneous Coronary Intervention to Long-Term Outcomes After Thrombolytic Administration in Acute Myocardial Infarction. Circulation 2002; 105:1909-1913, Blomley M J K, Dawson P. Bolus dynamics: theoretical and experimental aspects. The British Journal of Radiology 1997; 70:351-359, Rausch M, Scheffler K, Rudin M, Radu E W. Analysis of input functions from different arterial branches with gamma variate functions and cluster analysis for quantitative blood volume measurements. Magnetic Resonance Imaging 2000; 18:1235-1243.
Perfusion is visualized in medical diagnostic equipments based on advanced imaging techniques, in particular Echography, MRI, Angiography, PET, SPECT; images are generally obtained after infusion of a contrast agent that is created to be particularly well visible in the specific imaging modality. Such a contrast agent is a marker for blood and therefore permits to visualize the tissue uptake of blood while imaging as an increase of the brightness of the tissue, as shown in
This approach has however several major drawbacks as the perfusion is a measure of brightness and not of blood flow. Although brightness is related to the amount of contrast agent and therefore of blood, this relation is, in fact, not absolute and depends on several settings that are not controllable and/or normally not reproducible with confidence. Furthermore no information can be derivable on the capacity of a perfused object or organ to react to a demand of an increased fluid flow.
It is thus another object of the present invention to provide for a method for determining accurate and reproducible spatial perfusion measurements.
The applicant has now observed that a synergic combination of differential flow analysis and perfusion imaging can surprisingly contribute to solve the problems associated to both. In fact the use of perfusion imaging to measure flow properties allows to focus directly on microcirculation, and to evidence the spatial distribution of microcirculation flow thus solving the main drawbacks of differential flow analysis in general and CFR in particular. On the other hand, the application of the flow reserve concept to the perfusion measures implies that a microcirculation flow of an area is evaluated, during stress, relatively to the same area at rest. A target body is thus used as reference for itself. In medical applications that means that a patient is used as control for her/himself thus solving the main drawback of perfusion imaging.
The invention reaches the aims with a method for generating images representatives of the flow potential of a permeable body comprising the following steps:
Thanks to the method according to the invention it is thus possible to build, from at least two sequences of digital images, such as for example echographic loops, an image having pixels or group of pixels arranged in a pixel array in the correct or approximately correct spatial relation to the other pixels or group of pixels as their spatial relation existing in the real object and with a value representative of one or more parameters related to the flow potential of corresponding points or area of the real object. In this way an immediate grasp of a zone with poor flow capability (reserve) can be determined, especially if the resulting image is superimposed on an image of the body under investigation, for example by advantageously varying the opacity of such image as taught in the international application published with the number WO2005/054898.
Quantification images of the spatial distribution of flow can be determined, for example, by following the teachings of the European patent application published with number EP-A-1519315 or any other known method which allows to calculate images representative of the perfusion.
The at least two quantification images are typically aligned so that pixel values of one image can be compared to homologous pixel values of the other image, for example by deforming one or both images to allow cross reference points identified on both images to overlap. Such reference points could be landmarks, i.e. representative points or segments identified on each image, like, for example, in medical applications, easily discernible anatomic features. In cardiology images, such landmarks could be, for example, the two extremities of the annulus and the cardiac apex. Alternatively or in combination the images can be aligned manually or automatically using optimal-likelihood-based processing.
Advantageously the at least two quantification images are combined through a non-linear software and/or hardware device, such as a divider and/or a multiplier and/or a logarithmic and/or a cross-correlation circuit or the like.
Preferably the step of combining the two quantification images comprises calculating the ratio of pixel values of the second image to corresponding pixel values of the first image or vice versa to obtain an image where some or all the pixels have values corresponding to such ratio. One or more thresholds may be defined to determine which pixels of the generated image(s) are a combination of the corresponding pixels of the first and second image and/or which pixels of the generated image(s) correspond to pixels related to only one of the two images and/or are filtered out. For example by neglecting and/or correcting values below such threshold(s) noise can be filtered improving the quality of the generated image.
The step of extracting and/or calculating at least one quantification image from each sequence of images typically comprises one or more steps selected from the group consisting of:
The estimation function is typically of the form y(t)=A(1−exp(−Bt)), where y(t) is the pixel value depending from time, t is the time at which the pixel value has been determined in the image and A and B are parameters giving the best fit of said estimation function.
The parameters may be imaged in a two-dimensional or a three-dimensional image, or in any known representation of a function of one, two, or more variables with pixel values comprising the brightness of black and white digital images or one or more variables of colour digital images like hue, saturation, colour or the like.
According to an embodiment, more quantification images are extracted and/or calculated from each sequence of images, more images being generated by combining corresponding images at rest and stress condition. Alternatively or in combination only one image is generated, such image being the ratio of two images extracted/calculated from a combination of images extracted and/or calculated respectively from the sequence of images at stress and from the sequence of images at rest.
Advantageously the generated image(s) is/are displayed overlaid with the image(s) of the first and/or the second sequence of images and/or with the corresponding quantification image(s), for example by varying the opacity of such images.
The images of the sequences may echographic or MRI or SPECT or PET or X-Ray images or the like and may be, for example, obtained with one or more imaging modes selected from the group consisting of: Doppler, power Doppler, B-mode, Harmonic imaging, Contrast imaging.
According to an embodiment the permeable body is a biological tissue, the sequences of images being representative of the spatial distribution of blood flow in such tissue. Particularly the permeable body is the heart, the sequences of images being representative of the blood perfusion in the myocardium, for example images having brightness values related to the concentration of a contrast media perfusing the myocardium at the time the images are taken.
Advantageously for each sequence of images representative of a condition of the heart, a perfusion image is determined, such perfusion image giving a synthetic spatial representation of the perfusion process of at least part of the myocardium at such condition. One or more differential perfusion images representative of the capacity of the myocardium to react to a demand for an increased blood flow may be determined by combining perfusion images obtained from sequences of images of the myocardium at rest and hyperemic condition.
“Extracting”, as used herein, including use in the claims, means extracting and/or calculating in the context of a quantification image.
“Corrected”, as used herein, including use in the claims, means correcting and/or neglecting values below a threshold to filter noise in a generated image.
Further improvements of the invention will form the subject of the dependent claims.
The characteristics of the invention and the advantages derived therefrom will be more apparent from the following description of non-limiting embodiments, illustrated in the annexed drawings.
The invention relates to a method for generating images representative of the flow potential of a permeable body. The following steps are part of the disclosed method. First, providing a first sequence of digital images of the body perfused by a fluid at a rest condition. Then extracting a first quantification image of the spatial distribution of flow of the fluid in the body at the rest condition, the first quantification image being defined by pixel values. Next, providing a second sequence of digital images of the body perfused by the fluid at a stress condition. Then extracting a second quantification image of the spatial distribution of flow of the fluid in the body at the stress condition, the second quantification image being defined by pixel values. Then, combining the two quantification images to obtain an image defined by pixel values.
For the purposes of promoting an understanding of the disclosure, reference will now be made to the embodiments illustrated in the drawings and specific language will be used to describe the same. It will nevertheless be understood that no limitation of the scope of the disclosure is thereby intended, such alterations and further modifications in the illustrated device and its use, and such further applications of the principles of the disclosure as illustrated therein being contemplated as would normally occur to one skilled in the art to which the disclosure relates.
The invention will be now described with reference to bi-dimensional ultrasound images of organs, particularly the heart, however the skilled person would appreciate that the inventive concept can be applied to process any kind of sequence of images of bodies or regions perfused by a fluid from which quantification images of the spatial distribution of flow can be determined.
With reference to
The method according to the invention is essentially based on the processing of at least a pair of perfusion clips, or image sequences, recorded from the same object or area at rest (clip A) and during stress (clip B), respectively. The first clip is used as the baseline, the second clip is thus used to evaluate the flow increase relatively to that baseline.
The processing can be summarized with the following exemplary steps:
Clip Quantification into Parametric Images:
Example results after the first processing step are shown in
Although the method according to the invention has been mainly described with reference to bi-dimensional images, it can be also used with three-dimensional perfusion imaging all without departing from the guiding principle of the invention disclosed above and claimed below.
While the preferred embodiment of the invention has been illustrated and described in the drawings and foregoing description, the same is to be considered as illustrative and not restrictive in character, it being understood that all changes and modifications that come within the spirit of the invention are desired to be protected.
| Number | Date | Country | Kind |
|---|---|---|---|
| EP07116539.3 | Sep 2007 | EP | regional |
