Intravoxel incoherent motionΒΆ

The intravoxel incoherent motion (IVIM) model describes diffusion and perfusion in the signal acquired with a diffusion MRI sequence that contains multiple low b-values. The IVIM model can be understood as an adaptation of the work of Stejskal and Tanner [Stejskal65] in biological tissue, and was proposed by Le Bihan [LeBihan84]. The model assumes two compartments: a slow moving compartment, where particles diffuse in a Brownian fashion as a consequence of thermal energy, and a fast moving compartment (the vascular compartment), where blood moves as a consequence of a pressure gradient. In the first compartment, the diffusion coefficient is \(\mathbf{D}\) while in the second compartment, a pseudo diffusion term \(\mathbf{D^*}\) is introduced that describes the displacement of the blood elements in an assumed randomly laid out vascular network, at the macroscopic level. According to [LeBihan84], \(\mathbf{D^*}\) is greater than \(\mathbf{D}\).

The IVIM model expresses the MRI signal as follows:


where \(\mathbf{b}\) is the diffusion gradient weighing value (which is dependent on the measurement parameters), \(\mathbf{S_{0}}\) is the signal in the absence of diffusion gradient sensitization, \(\mathbf{f}\) is the perfusion fraction, \(\mathbf{D}\) is the diffusion coefficient and \(\mathbf{D^*}\) is the pseudo-diffusion constant, due to vascular contributions.

In the following example we show how to fit the IVIM model on a diffusion-weighteddataset and visualize the diffusion and pseudo diffusion coefficients. First, we import all relevant modules:

import matplotlib.pyplot as plt

from dipy.reconst.ivim import IvimModel
from import read_ivim

We get an IVIM dataset using DIPY‘s data fetcher read_ivim. This dataset was acquired with 21 b-values in 3 different directions. Volumes corresponding to different directions were registered to each other, and averaged across directions. Thus, this dataset has 4 dimensions, with the length of the last dimension corresponding to the number of b-values. In order to use this model the data should contain signals measured at 0 bvalue.

img, gtab = read_ivim()

The variable img contains a nibabel NIfTI image object (with the data) and gtab contains a GradientTable object (information about the gradients e.g. b-values and b-vectors). We get the data from img using read_data.

data = img.get_data()
print('data.shape (%d, %d, %d, %d)' % data.shape)

The data has 54 slices, with 256-by-256 voxels in each slice. The fourth dimension corresponds to the b-values in the gtab. Let us visualize the data by taking a slice midway(z=33) at \(\mathbf{b} = 0\).

z = 33
b = 0

plt.imshow(data[:, :, z, b].T, origin='lower', cmap='gray',

Heat map of a slice of data

The region around the intersection of the cross-hairs in the figure contains cerebral spinal fluid (CSF), so it so it should have a very high \(\mathbf{f}\) and \(\mathbf{D^*}\), the area between the right and left is white matter so that should be lower, and the region on the right is gray matter and CSF. That should give us some contrast to see the values varying across the regions.

x1, x2 = 90, 155
y1, y2 = 90, 170
data_slice = data[x1:x2, y1:y2, z, :]

plt.imshow(data[x1:x2, y1:y2, z, b].T, origin='lower',
           cmap="gray", interpolation='nearest')

Heat map of the CSF slice selected.

Now that we have prepared the datasets we can go forward with the ivim fit. Instead of fitting the entire volume, we focus on a small section of the slice as selected aboove, to fit the IVIM model. First, we instantiate the Ivim model. Using a two-stage approach: first, a linear fit used to get quick initial guesses for the parameters \(\mathbf{S_{0}}\) and \(\mathbf{D}\) by considering b-values greater than split_b_D (default: 400))and assuming a mono-exponential signal. This is based on the assumption that at high b-values the signal can be approximated as a mono exponential decay and by taking the logarithm of the signal values a linear fit can be obtained. Another linear fit for S0 (bvals < split_b_S0 (default: 200)) follows and f is estimated using \(1 - S0_{prime}/S0\). Then a non-linear least squares fitting is performed to fit D_star and f. If the two_stage flag is set to True while initializing the model, a final non-linear least squares fitting is performed for all the parameters using Scipy’s leastsq or least_square function depending on which Scipy version you are using. All initializations for the model such as split_b_D are passed while creating the IvimModel. If you are using Scipy 0.17, you can also set bounds by setting bounds=([0., 0., 0., 0.], [np.inf, 1., 1., 1.])) while initializing the IvimModel. It is recommeded that you upgrade to Scipy 0.17 since the fitting results might at times return values which do not make sense physically (for example, a negative \(\mathbf{f}\)).

ivimmodel = IvimModel(gtab)

To fit the model, call the fit method and pass the data for fitting.

ivimfit =

The fit method creates a IvimFit object which contains the parameters of the model obtained after fitting. These are accessible through the model_params attribute of the IvimFit object. The parameters are arranged as a 4D array, corresponding to the spatial dimensions of the data, and the last dimension (of length 4) corresponding to the model parameters according to the following order : \(\mathbf{S_{0}, f, D^*, D}\).

ivimparams = ivimfit.model_params
print("ivimparams.shape : {}".format(ivimparams.shape))

As we see, we have a 20x20 slice at the height z = 33. Thus we have 400 voxels. We will now plot the parameters obtained from the fit for a voxel and also various maps for the entire slice. This will give us an idea about the diffusion and perfusion in that section. Let(i, j) denote the coordinate of the voxel. We have already fixed the z component as 33 and hence we will get a slice which is 33 units above.

i, j = 10, 10
estimated_params = ivimfit.model_params[i, j, :]

Next, we plot the results relative to the model fit. For this we will use the predict method of the IvimFit object to get the estimated signal.

estimated_signal = ivimfit.predict(gtab)[i, j, :]

plt.scatter(gtab.bvals, data_slice[i, j, :],
            color="green", label="Actual signal")
plt.plot(gtab.bvals, estimated_signal, color="red", label="Estimated Signal")

S0_est, f_est, D_star_est, D_est = estimated_params
text_fit = """Estimated \n S0={:06.3f} f={:06.4f}\n
            D*={:06.5f} D={:06.5f}""".format(S0_est, f_est, D_star_est, D_est)

plt.text(0.65, 0.50, text_fit, horizontalalignment='center',
         verticalalignment='center', transform=plt.gca().transAxes)
plt.legend(loc='upper right')

Plot of the signal from one voxel.

Now we can map the perfusion and diffusion maps for the slice. We will plot a heatmap showing the values using a colormap. It will be useful to define a plotting function for the heatmap here since we will use it to plot for all the IVIM parameters. We will need to specify the lower and upper limits for our data. For example, the perfusion fractions should be in the range (0,1). Similarly, the diffusion and pseudo-diffusion constants are much smaller than 1. We pass an argument called variable to out plotting function which gives the label for the plot.

def plot_map(raw_data, variable, limits, filename):
    lower, upper = limits
    plt.title('Map for {}'.format(variable))
    plt.imshow(raw_data.T, origin='lower', clim=(lower, upper),
               cmap="gray", interpolation='nearest')

Let us get the various plots so that we can visualize them in one page

plot_map(ivimfit.S0_predicted, "Predicted S0", (0, 10000), "predicted_S0.png")
plot_map(data_slice[:, :, 0], "Measured S0", (0, 10000), "measured_S0.png")
plot_map(ivimfit.perfusion_fraction, "f", (0, 1), "perfusion_fraction.png")
plot_map(ivimfit.D_star, "D*", (0, 0.01), "perfusion_coeff.png")
plot_map(ivimfit.D, "D", (0, 0.001), "diffusion_coeff.png")

Heatmap of S0 predicted from the fit


Heatmap of measured signal at bvalue = 0.


Heatmap of perfusion fraction values predicted from the fit


Heatmap of perfusion coefficients predicted from the fit.


Heatmap of diffusion coefficients predicted from the fit


[Stejskal65]Stejskal, E. O.; Tanner, J. E. (1 January 1965). “Spin Diffusion Measurements: Spin Echoes in the Presence of a Time-Dependent Field Gradient”. The Journal of Chemical Physics 42 (1): 288. Bibcode: 1965JChPh..42..288S. doi:10.1063/1.1695690.
[LeBihan84](1, 2) Le Bihan, Denis, et al. “Separation of diffusion and perfusion in intravoxel incoherent motion MR imaging.” Radiology 168.2 (1988): 497-505.

Example source code

You can download the full source code of this example. This same script is also included in the dipy source distribution under the doc/examples/ directory.