Evaluating the results of tractography algorithms is one of the biggest challenges for diffusion MRI. One proposal for evaluation of tractography results is to use a forward model that predicts the signal from each of a set of streamlines, and then fit a linear model to these simultaneous predictions [Pestilli2014].

We will use streamlines generated using probabilistic tracking on CSA peaks. For brevity, we will include in this example only streamlines going through the corpus callosum connecting left to right superior frontal cortex. The process of tracking and finding these streamlines is fully demonstrated in the Connectivity Matrices, ROI Intersections and Density Maps example. If this example has been run, we can read the streamlines from file. Otherwise, we’ll run that example first, by importing it. This provides us with all of the variables that were created in that example:

```
from mpl_toolkits.axes_grid1 import AxesGrid
import matplotlib
import matplotlib.pyplot as plt
import dipy.tracking.life as life
from dipy.viz import window, actor, colormap as cmap
import numpy as np
import os.path as op
from dipy.io.streamline import load_trk
import dipy.core.optimize as opt
if not op.exists('lr-superiorfrontal.trk'):
from streamline_tools import *
else:
# We'll need to know where the corpus callosum is from these variables:
from dipy.core.gradients import gradient_table
from dipy.data import get_fnames
from dipy.io.gradients import read_bvals_bvecs
from dipy.io.image import load_nifti_data, load_nifti
hardi_fname, hardi_bval_fname, hardi_bvec_fname = get_fnames('stanford_hardi')
label_fname = get_fnames('stanford_labels')
t1_fname = get_fnames('stanford_t1')
data, affine, hardi_img = load_nifti(hardi_fname, return_img=True)
labels = load_nifti_data(label_fname)
t1_data = load_nifti_data(t1_fname)
bvals, bvecs = read_bvals_bvecs(hardi_bval_fname, hardi_bvec_fname)
gtab = gradient_table(bvals, bvecs)
cc_slice = labels == 2
# Read the candidates from file in voxel space:
candidate_sl_sft = load_trk('lr-superiorfrontal.trk', 'same')
candidate_sl_sft.to_vox()
candidate_sl = candidate_sl_sft.streamlines
```

The streamlines that are entered into the model are termed ‘candidate streamlines’ (or a ‘candidate connectome’):

Let’s visualize the initial candidate group of streamlines in 3D, relative to the anatomical structure of this brain:

```
# Enables/disables interactive visualization
interactive = False
candidate_streamlines_actor = actor.streamtube(candidate_sl,
cmap.line_colors(candidate_sl))
cc_ROI_actor = actor.contour_from_roi(cc_slice, color=(1., 1., 0.),
opacity=0.5)
vol_actor = actor.slicer(t1_data)
vol_actor.display(x=40)
vol_actor2 = vol_actor.copy()
vol_actor2.display(z=35)
# Add display objects to canvas
scene = window.Scene()
scene.add(candidate_streamlines_actor)
scene.add(cc_ROI_actor)
scene.add(vol_actor)
scene.add(vol_actor2)
window.record(scene, n_frames=1,
out_path='life_candidates.png',
size=(800, 800))
if interactive:
window.show(scene)
```

Next, we initialize a LiFE model. We import the `dipy.tracking.life`

module,
which contains the classes and functions that implement the model:

```
fiber_model = life.FiberModel(gtab)
```

Since we read the streamlines from a file, already in the voxel space, we do not need to transform them into this space. Otherwise, if the streamline coordinates were in the world space (relative to the scanner iso-center, or relative to the mid-point of the AC-PC-connecting line), we would use this:

```
inv_affine = np.linalg.inv(hardi_img.affine)
```

the inverse transformation from world space to the voxel space as the affine for the following model fit.

The next step is to fit the model, producing a `FiberFit`

class instance,
that stores the data, as well as the results of the fitting procedure.

The LiFE model posits that the signal in the diffusion MRI volume can be explained by the streamlines, by the equation

\[y = X\beta\]

Where \(y\) is the diffusion MRI signal, \(\beta\) are a set of weights on the streamlines and \(X\) is a design matrix. This matrix has the dimensions \(m\) by \(n\), where \(m=n_{voxels} \cdot n_{directions}\), and \(n_{voxels}\) is the set of voxels in the ROI that contains the streamlines considered in this model. The \(i^{th}\) column of the matrix contains the expected contributions of the \(i^{th}\) streamline (arbitrarily ordered) to each of the voxels. \(X\) is a sparse matrix, because each streamline traverses only a small percentage of the voxels. The expected contributions of the streamline are calculated using a forward model, where each node of the streamline is modeled as a cylindrical fiber compartment with Gaussian diffusion, using the diffusion tensor model. See [Pestilli2014] for more detail on the model, and variations of this model.

```
fiber_fit = fiber_model.fit(data, candidate_sl, affine=np.eye(4))
```

The `FiberFit`

class instance holds various properties of the model fit. For
example, it has the weights \(\beta\), that are assigned to each streamline. In
most cases, a tractography through some region will include redundant
streamlines, and these streamlines will have \(\beta_i\) that are 0.

```
fig, ax = plt.subplots(1)
ax.hist(fiber_fit.beta, bins=100, histtype='step')
ax.set_xlabel('Fiber weights')
ax.set_ylabel('# fibers')
fig.savefig('beta_histogram.png')
```

We use \(\beta\) to filter out these redundant streamlines, and generate an optimized group of streamlines:

```
optimized_sl = list(np.array(candidate_sl)[np.where(fiber_fit.beta > 0)[0]])
scene = window.Scene()
scene.add(actor.streamtube(optimized_sl, cmap.line_colors(optimized_sl)))
scene.add(cc_ROI_actor)
scene.add(vol_actor)
window.record(scene, n_frames=1, out_path='life_optimized.png',
size=(800, 800))
if interactive:
window.show(scene)
```

The new set of streamlines should do well in fitting the data, and redundant streamlines have presumably been removed (in this case, about 50% of the streamlines).

But how well does the model do in explaining the diffusion data? We can
quantify that: the `FiberFit`

class instance has a predict method, which
can be used to invert the model and predict back either the data that was used
to fit the model, or other unseen data (e.g. in cross-validation, see
kfold_xval).

Without arguments, the `.predict()`

method will predict the diffusion signal
for the same gradient table that was used in the fit data, but `gtab`

and
`S0`

keyword arguments can be used to predict for other acquisition schemes
and other baseline non-diffusion-weighted signals.

```
model_predict = fiber_fit.predict()
```

We will focus on the error in prediction of the diffusion-weighted data, and calculate the root of the mean squared error.

```
model_error = model_predict - fiber_fit.data
model_rmse = np.sqrt(np.mean(model_error[:, 10:] ** 2, -1))
```

As a baseline against which we can compare, we calculate another error term. In this case, we assume that the weight for each streamline is equal to zero. This produces the naive prediction of the mean of the signal in each voxel.

```
beta_baseline = np.zeros(fiber_fit.beta.shape[0])
pred_weighted = np.reshape(opt.spdot(fiber_fit.life_matrix, beta_baseline),
(fiber_fit.vox_coords.shape[0],
np.sum(~gtab.b0s_mask)))
mean_pred = np.empty((fiber_fit.vox_coords.shape[0], gtab.bvals.shape[0]))
S0 = fiber_fit.b0_signal
```

Since the fitting is done in the demeaned S/S0 domain, we need to add back the mean and then multiply by S0 in every voxel:

```
mean_pred[..., gtab.b0s_mask] = S0[:, None]
mean_pred[..., ~gtab.b0s_mask] =\
(pred_weighted + fiber_fit.mean_signal[:, None]) * S0[:, None]
mean_error = mean_pred - fiber_fit.data
mean_rmse = np.sqrt(np.mean(mean_error ** 2, -1))
```

First, we can compare the overall distribution of errors between these two alternative models of the ROI. We show the distribution of differences in error (improvement through model fitting, relative to the baseline model). Here, positive values denote an improvement in error with model fit, relative to without the model fit.

```
fig, ax = plt.subplots(1)
ax.hist(mean_rmse - model_rmse, bins=100, histtype='step')
ax.text(0.2, 0.9, 'Median RMSE, mean model: %.2f' % np.median(mean_rmse),
horizontalalignment='left',
verticalalignment='center',
transform=ax.transAxes)
ax.text(0.2, 0.8, 'Median RMSE, LiFE: %.2f' % np.median(model_rmse),
horizontalalignment='left',
verticalalignment='center',
transform=ax.transAxes)
ax.set_xlabel('RMS Error')
ax.set_ylabel('# voxels')
fig.savefig('error_histograms.png')
```

Second, we can show the spatial distribution of the two error terms, and of the improvement with the model fit:

```
vol_model = np.ones(data.shape[:3]) * np.nan
vol_model[fiber_fit.vox_coords[:, 0],
fiber_fit.vox_coords[:, 1],
fiber_fit.vox_coords[:, 2]] = model_rmse
vol_mean = np.ones(data.shape[:3]) * np.nan
vol_mean[fiber_fit.vox_coords[:, 0],
fiber_fit.vox_coords[:, 1],
fiber_fit.vox_coords[:, 2]] = mean_rmse
vol_improve = np.ones(data.shape[:3]) * np.nan
vol_improve[fiber_fit.vox_coords[:, 0],
fiber_fit.vox_coords[:, 1],
fiber_fit.vox_coords[:, 2]] = mean_rmse - model_rmse
sl_idx = 49
fig = plt.figure()
fig.subplots_adjust(left=0.05, right=0.95)
ax = AxesGrid(fig, 111,
nrows_ncols=(1, 3),
label_mode="1",
share_all=True,
cbar_location="top",
cbar_mode="each",
cbar_size="10%",
cbar_pad="5%")
ax[0].matshow(np.rot90(t1_data[sl_idx, :, :]), cmap=matplotlib.cm.bone)
im = ax[0].matshow(np.rot90(vol_model[sl_idx, :, :]), cmap=matplotlib.cm.hot)
ax.cbar_axes[0].colorbar(im)
ax[1].matshow(np.rot90(t1_data[sl_idx, :, :]), cmap=matplotlib.cm.bone)
im = ax[1].matshow(np.rot90(vol_mean[sl_idx, :, :]), cmap=matplotlib.cm.hot)
ax.cbar_axes[1].colorbar(im)
ax[2].matshow(np.rot90(t1_data[sl_idx, :, :]), cmap=matplotlib.cm.bone)
im = ax[2].matshow(np.rot90(vol_improve[sl_idx, :, :]),
cmap=matplotlib.cm.RdBu)
ax.cbar_axes[2].colorbar(im)
for lax in ax:
lax.set_xticks([])
lax.set_yticks([])
fig.savefig("spatial_errors.png")
```

This image demonstrates that in many places, fitting the LiFE model results in substantial reduction of the error.

Note that for full-brain tractographies *LiFE* can require large amounts of
memory. For detailed memory profiling of the algorithm, based on the
streamlines generated in example_probabilistic_fiber_tracking, see this
IPython notebook.

For the Matlab implementation of LiFE, head over to Franco Pestilli’s github webpage.

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.