Method and system for mapping tissue status of acute stroke

• US 8,942,451 B2
• Filed: 11/13/2009
• Issued: 01/27/2015
• Est. Priority Date: 11/14/2008
• Status: Active Grant

• Current Assignee: Apollo Medical Imaging Technology Pty., Ltd.
• Original Assignee: Apollo Medical Imaging Technology Pty., Ltd.
• Inventors: Yang, Qing
• Primary Examiner(s): Park, Chan
• Assistant Examiner(s): Kholdebarin, Iman K
• Application Number:
  US13/128,645
• Publication Number:
  US 20110229003A1
• Time in Patent Office: 1,901 Days
• Field of Search: 382128-132
• US Class Current: 382/131
• CPC Class Codes: A61B 5/055 involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
• CPC Class Codes: A61B 5/416 the spleen
• CPC Class Codes: A61B 6/501 for diagnosis of the head, e.g. neuroimaging or craniography
• CPC Class Codes: A61B 6/507 for determination of haemodynamic parameters, e.g. perfusion CT
• CPC Class Codes: A61B 6/5217 extracting a diagnostic or physiological parameter from medical diagnostic data
• CPC Class Codes: A61B 6/5247 combining images from an ionising-radiation diagnostic technique and a non-ionising radiation diagnostic technique, e.g. X-ray and ultrasound
• CPC Class Codes: G06T 2207/10072 Tomographic images
• CPC Class Codes: G06T 2207/30104 Vascular flow; Blood flow; Perfusion
• CPC Class Codes: G06T 7/0012 Biomedical image inspection
• CPC Class Codes: G06T 7/11 Region-based segmentation
• CPC Class Codes: G06T 7/136 involving thresholding
• CPC Class Codes: G16H 50/30 for calculating health indices; for individual health risk assessment

Abstract

The current invention provides a method of identifying a ischemic lesion. The method includes loading perfusion imaging data into an electronic memory element and deriving perfusion maps from the perfusion imaging data, where the perfusion maps include a cerebral blood volume (CBV) map and an arterial delay time (DT) map, which utilize arterial delay and dispersion effects. Ischemic pixels are determined from the perfusion imaging data, where the DT is greater than a predetermined first threshold value and the CBV is below a second threshold value and the infarct portion of the ischemic lesion is determined, where DT is greater than a predetermined third threshold value and/or the CBV is below a forth threshold value. A cluster analysis is applied to all of the determined ischemic lesion and infarct pixels and the penumbra is then determined, where mismatch regions between the ischemic lesion and the infarct core define the penumbra.

Claims

1. A method of identifying ischemic lesions in a subject, by operating a computer program on perfusion imaging data input to a computer comprising:

a. loading said perfusion imaging data into an electronic memory means, wherein said perfusion imaging data contains information of a contrast agent passing through a region of interest (ROI), wherein said ROI comprises tissue;

b. measuring a global arterial input function AIF from a normal major artery, wherein said AIF is an intensity profile measured against time;

c. measuring a tissue contrast agent curve C(t) in said tissue, wherein said C(t) is an intensity profile measured against time;

d. deriving perfusion maps by deconvolution of said AIF from said C(t) on a pixel-by-pixel basis using a delay and dispersion compensated deconvolution method, wherein said perfusion maps comprise an arterial delay time (DT) map and cerebral blood volume (CBV), cerebral blood flow (CBF) and mean transit time (MTT) maps;

e. determining ischemic lesion pixels from said perfusion imaging data, wherein said DT is greater than a predetermined first threshold value and said CBV is below a second threshold value.

f. applying a cluster analysis to said ischemic lesion pixels by removing small islands or filling small holes, wherein the said small island[s] or small holes have a maximum cluster size below a predetermined fifth threshold value.

2. The method according to claim 1 further comprising the step of determining the infarct portion of said ischemic lesion, wherein (i) said DT is greater than a predetermined third threshold value, or (ii) said CBV is below a forth threshold value, or (i) and (ii).

3. The method according to claim 2 may further comprise the step of applying a cluster analysis to said infarct pixels by removing small islands or filling small holes, wherein the said small island or small holes have a maximum cluster size below the predetermined fifth threshold value.

4. The method according to claim 2 further comprising the step of determining a penumbra by the mismatch regions between said ischemic lesion and said infarct.

5. The method according to claim 4 further comprising the step of determining a penumbra volume as a percentage of the said ischemic lesion volume.

6. The method according to claim 1, wherein:

a. said predetermined first threshold value is approximately 3 to 4 seconds;

b. said predetermined second threshold value is approximately 9 ml/100 g.

7. The method according to claim 2, wherein:

a. said predetermined third threshold value is approximately 10 seconds;

b. said predetermined forth threshold value is approximately 1.5 ml/100 g;

c. alternatively, said predetermined forth threshold value is approximately 50% of the average CBV value measured from unaffected normal tissue of said subject.

8. The method according to claim 1, wherein said predetermined fifth threshold value is approximately 3 to 5 mm.

9. The method according to claim 1, in which step d) is performed by:

a. calculating a tissue impulse residue function (IRF) by deconvolution of said AIF from said C(t) using a model-free deconvolution method, wherein the maximum of the IRF appears at certain time point, Tmax;

b. looping through a series of delay time values, DTi, ranging from 0 to Tmax, wherein for each delay time value, an arterial transport function with a delay time DTi and a known relative dispersion factor is convolved with said AIF to produce an AIFi, wherein an IRFi is calculated by deconvolution of said AIFi from said C(t) using said model-free deconvolution method, wherein the maximum of the IRFi appears at Tmax(i);

c. determining DT by the minimum DTi value which produces Tmax(i)=0;

wherein the corresponding IRFi is recorded as IRFo;

d. determining CBF and CBV by the maximum and integral of said IRFo respectively, wherein MTT=CBV/CBF.

10. The method according to claim 1, in which step d) may be performed alternatively by:

a. simulating a tissue input function AIF_t by convolving said AIF with a first model for a vascular transport function taking into account delay and dispersion effects;

b. simulating a tissue curve C_s(t) by convolving said AIF with a second model for a tissue transport function;

c. using a least squares method to fit the said simulated C_s(t) to said measured tissue curve C(t) by optimizing the values of at least four adjustable parameters;

d. using a model-free deconvolution method to estimate initial values of said adjustable parameters for said least squares fitting process in order to derive optimized values of said adjustable parameters; and

e. calculating perfusion maps from said optimized values of adjustable parameters.

11. The method of claim 1, wherein said AIF is scaled upward according to a venous output function (VOF), wherein said VOF is based on a measured contrast intensity profile in a vein draining from said ROI.

12. A system of identifying ischemic lesions in a subject, the system comprising:

scanning means for acquiring a perfusion image data of the subject, wherein a contrast agent is administered to the subject during a dynamic imaging scan;

storage means for retrieving or receiving image data from the scanning means;

processor means comprising;

a. loading said perfusion imaging data into an electronic memory means, wherein said perfusion imaging data contains information of a contrast agent passing through a region of interest (ROI), wherein said ROI comprises tissue;

b. measuring a global arterial input function AIF from a normal major artery, wherein said AIF is an intensity profile measured against time;

c. measuring a tissue contrast agent curve C(t) in said tissue, wherein said C(t) is an intensity profile measured against time;

d. deriving perfusion maps by deconvolution of said AIF from said C(t) on a pixel-by-pixel basis using a delay and dispersion compensated deconvolution method, wherein said perfusion maps comprise an arterial delay time (DT) map and cerebral blood volume (CBV), cerebral blood flow (CBF) and mean transit time (MTT) maps;

e. determining ischemic lesion pixels from said perfusion imaging data, wherein said DT is greater than a predetermined first threshold value and said CBV is below a second threshold value.

f. applying a cluster analysis to said ischemic lesion by removing small islands or filling small holes, wherein the said small island[s] or small holes have a maximum cluster size below a predetermined fifth threshold value.

13. The system according to claim 12 further comprising the step of determining the infarct portion of said ischemic lesion, wherein (i) said DT is greater than a predetermined third threshold value, or (ii) said CBV is below a forth threshold value, or (i) and (ii).

14. The system according to claim 13 may further comprise the step of applying a cluster analysis to said infarct pixels by removing small islands or filling small holes, wherein the said small island or small holes have a maximum cluster size below a predetermined fifth threshold value.

15. The system according to claim 13 further comprising the step of determining a penumbra by the mismatch regions between said ischemic lesion and said infarct.

16. The system according to claim 15 further comprising the step of determining a penumbra volume as a percentage of the said ischemic lesion volume to guide treatment of the acute stroke patient.

17. The system according to claim 12, in which the scanning means is at least one of a computed tomography (CT) imaging system and a magnetic resonance imaging (MRI) system. The storage means is a data storage system such as a Picture Archiving Communications System (PACS).