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11 3D Medical Imaging

463

Given a uniform grid of control points φi,j,k , we can produce a free form deformation of space using a local transformation:

3

3

3

 

Tlocal(x, y, z) =

 

Bl (u)Bm(v)Bn(w)φi+l,j +m,k+n

(11.10)

l=0 m=0 n=0

 

where i, j, k is the index of the node preceding x, y, z and u, v, w represents the fraction of the grid beyond the point that the position x, y, z is located. The free form deformation can interpolate the whole of the domain smoothly and has some nice properties. It is locally controlled, which means that the movement of a control point only affects the local region. This makes it more computationally efficient than methods such as the thin-plate spline, where motion of a single landmark affects the whole of the domain. The complexity of the free form deformation can be controlled by setting the control point spacing.

11.4.2 Points and Features Used for the Registration

Having chosen an appropriate transformation for our problem, the next step is to decide what type of features should be used to calculate the registration. There will, in general, be some sort of corresponding anatomical points or regions. These can be categorized by their dimension.

11.4.2.1 Landmark Features

The simplest feature to consider is the landmark, where landmarks are well-defined points in 3D space within the 3D images to be registered. If corresponding landmarks can be found in the two images, these can form the basis of the registration. Landmarks may be anatomical features, such as the centers of the eyes, bony protrusions, or crossing points of vessels. Alternatively, there may be markers attached to the patient for the purposes of registration. It is common for these landmarks to be called fiducial points or, more succinctly, fiducials.

The points to be aligned are represented by two corresponding landmark sets, {xi }, {yi }. Given one of the above spatial transforms, T, the standard similarity function is the target registration error, TRE, and we wish to find an instance of the selected class of transformations, such that this error is minimized:

TRE

 

=

min

 

Tx

i

y

i

2.

(11.11)

 

T

 

 

 

 

i

The squared norm can be replaced by more general functions. Note that we assume that landmarks are already matched, in general this might require either manual intervention, or algorithmic search.

464

P.G. Batchelor et al.

11.4.2.2 Surface-Based Registration

Rather than using 3D points, one could imagine a registration based on linear features, such as blood vessels or ridges on the surface of an object. In practice, such registrations are rare and it is more common to use surfaces. This approach was first proposed for medical imaging by Pelizzari et al. [61] as the head and hat algorithm. This led to a number of techniques to register 3D images using distance maps, or chamfer maps, which are images showing the distance to a given surface. These techniques have been very much taken over by intensity-based registration for fully 3D volumes, but there is still a place for surface matching in image-guided surgery, which we will discuss later, and in situations where an accurate segmentation of two images has been created. The surface may be a polygonal surface or a set of surface points, but typically the preoperative surface will be triangulated and intraoperative measurements will be points. A surface-based similarity measure can be generated as the sum-of-squared distance from the surface points to the nearest points on the triangulated surface.

11.4.2.3 Intensity-Based Registration

One of the most successful methods in medical image registration in the last few decades has been the use of intensity-based similarity measures. Given that we have a transformation T from image IA(x) to image IB (y), we are able to calculate corresponding voxel intensities. For a given voxel at position x in image IA(x) the corresponding point in image IB will be IB (T(x)). We can now start to calculate some image statistics in the region of the overlap, , between the two images.

For example, if we are trying to register images from the same modality and patient, we could assume that corresponding voxels will have the same intensity. This means that, at registration, all voxels should be equal and we can minimize a cost function, CSSD, to give:

C

T

min

1

 

I

 

(x)

I

 

T(x) 2

(11.12)

N x

 

 

SSD

( ) =

T

 

A

 

 

B

 

 

where N is the number of voxels in the overlap. This is simply the mean sum of squared differences of intensities between the images. Thus, by minimizing CSSD(T) over the parameters of our transformation, T, we can achieve registration without needing to extract landmarks.

If we know the voxel intensities of the two images are an increasing function of each other, but we can’t be sure that they have the same intensities, then perhaps cross-correlation would be a more appropriate measure. When the relationship between intensities in the two images is not known we can use information theoretic measures to provide a similarity measure. We start by producing a 2D histogram. For each corresponding pixel we have an intensity IA and an intensity IB . These form a point on a graph of intensity in image type A (CT, say) vs image type B (MRI,