IMPLANTABLE ARRAY WITH A REFERENCE STRUCTURE AND A METHOD OF IMAGING THE SAME

Abstract

An implantable array suitable for being placed in anatomic tissue of a human or animal body is provided. The implantable array has a substrate and a reference structure, the reference structure being formed by a number of notches arranged in at least one outer edge of the substrate, the reference structure defines a spatial relationship with predefined points of the array.

Claims

1. An implantable array suitable for being placed in anatomic tissue of a human or animal body, comprising a substrate, and a reference structure (5), the reference structure being formed by a number of notches (51, 52, 53, 54) arranged in at least one outer edge of the substrate, the reference structure (5) defining a spatial relationship with predefined points (2) of the array.

2. The implantable array of claim 1, wherein the notches (51, 52, 53, 54) are arranged in at least two adjacent outer edges of the array.

3. The implantable array of claim 1, wherein each notch (51, 52, 53, 54) is spaced apart from each other notch (51, 52, 53, 54).

4. The implantable array of claim 2, wherein the spatial relationship is a grid (7) over a surface (8) of the array.

5. The implantable array of claim 1, wherein the grid (7) is a rectangular, regular grid (7).

6. The implantable array of claim 1, wherein the location is at least one of an electrode contact, a fluidic interface, and a point of geometrical significance.

7. The implantable array of claim 1, wherein the implantable array comprises at least one layer of a polymer, in particular selected from the group comprising silicone rubber, polyurethane, polyimide, epoxy, liquid crystal polymer, and parylene.

8. The implantable array of claim 1, wherein the array is an electrode array.

9. The implantable array of claim 1, wherein the array is a planar and flexible array.

10. A method of magnetic resonance imaging, MRI, of the implantable array of claim 1, when implanted in a human or animal body, the method comprising: acquiring at least one first T2-weighted image of a body region comprising the implantable array, and at least one second T2-weighted image of the body region comprising the implantable array, the first image being acquired at a first echo time, TE_1, the first echo time being smaller than the transverse relaxation time, T2*, of silicone, the second T2-weighted image being acquired at a second echo time, TE_2, the second echo time being selected to be equal to or greater than the transverse relaxation time, T2*, of the substrate, but smaller than the transverse relaxation time of body tissue, generating a difference image on the basis of the at least one second image and the at least one first image, wherein the first sequence and the second sequence comprise identical relaxation time, TR, inversion time, TI, and flip angle (α) setting.

11. The method of claim 10, wherein the at least one first and second images are acquired on the basis of first and second predetermined gradient echo sequences.

Description

BRIEF DESCRIPTION OF THE DRAWING

[0029] The invention and embodiments thereof will be described below in further detail in connection with the drawing.

[0030] FIG. 1 illustrates schematically the implantable electrode array according to an embodiment of the invention,

[0031] FIG. 2 illustrates the implantable electrode array according to embodiments of the invention,

[0032] FIG. 3 illustrates sectional view of the implantable electrode array according to an embodiment of the invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0033] FIG. 1 and FIG. 2 illustrate embodiments of the implantable array, that is a planar implantable electrode array. The implantable electrode array comprises at least one substrate 1 made from a biocompatible polymer. The polymer can be selected from the group comprising silicone rubber, polyurethane, polyimide, epoxy, liquid crystal polymer, and parylene.

[0034] The implantable electrode array is preferably flexible such that it can adapt its form to the form of the location in the cortex of a human or animal where it is placed. The electrode array comprises sensor electrode contacts 2 of diameter c on its surface 8. The sensor contacts are equidistant to each other, and are arranged in columns and rows, i.e., they define a regular rectangular grid over the surface of the electrode array.

[0035] The electrode contacts 2 may be located in apertures 6 in the polymer 1 of a diameter smaller than diameter c, refer to FIG. 3. Typical diameters c of the electrode contacts 2 are 4 mm. The apertures 6 may have a diameter of 2.3 mm, refer to FIG. 2A. Typical electrode arrays may comprise e.g. 3×3 electrode contacts or 3×6 electrode contacts, depending on the intended application. A typical spacing between two electrode contacts 2 (interelectrode spacing) may be 10 mm. Microelectrode arrays, according to a further embodiment of the invention, may have contacts 4 with diameters of about 0.3 mm, refer to FIG. 2B.

[0036] Additionally to, or instead of the contacts 2, other predefined points of interest on the implant array may be referenced via the reference structure. Thus, most generally, the predefined points 2 which can be referenced by the patterns 51, 52, 53, 54, 55 may be [0037] a) electrical contacts 2, i.e., sensor contacts, whose material may be selected from metal, conductive polymer, carbon on the implantable array, as described above, [0038] b) fluidic interfaces (e.g., inlets or outlets for conveying liquids into the body, or out of the human or animal body), [0039] c) other points of particular geometrical significance for the physician.

[0040] The implantable electrode array further comprises a reference structure 5. The reference structure 5 is formed by notches 51, 52, 53, 54 along the four outer edges of the substrate 8 of the electrode array. The notches 51, 52, 53, 54 are distinct from each other and regularly spaced apart from each other. Each of these notches is concavely formed, i.e., forms a recess in the respective outer edge towards the inner of the array. All the notches 51, 52, 53, 54 have identical shape.

[0041] The notches 51, 52, 53, 54 are located at positions on straight elongated lines 7 through the contacts 2. The dimension of the notches may be the same as the diameter of the contacts.

[0042] In other words, the reference structure 5, i.e., the notches 51, 52, 53, 54 define a spatial relationship with the electrode contacts 2 of the implant array. The spatial relationship is a regular, rectangular grid 7 over a surface 8 of the array, wherein the electrode contacts are in the crossings of the grid lines.

[0043] In MRI of the electrode array, the edges thereof with the notches 51, 52, 53, 54 are visible, as long as the substrate 8 of the electrode array is visible. Since the notches 51, 52, 53, 54 define a grid over the surface 8 of the electrode array comprising the electrode contacts 2, the positions of the sensor contacts 2 can be determined as being located at the (imaginary) crossing points of the (imaginary) grid lines in the MRIs. Therefore, the notches 51, 52, 53, 54 can be used as reference structure 5 for localizing the electrode contacts 2 (or the other points of interest) in the MRIs, regardless whether or not the electrode contacts 2 themselves are correctly imaged in the MRIs.

[0044] In the following, the method of magnetic resonance imaging, MRI, of the implantable electrode array as described before, implanted in a human or animal body is outlined.

[0045] Hereto, T2-star (T2*=effective transverse relaxation time) weighted images are used, especially acquired with Gradient Echo (GRE) imaging sequences.

[0046] The substrate material (e.g., silicone) has a very short T2* at the clinical field strengths that are typically used for MRI (e.g., B=0.2 Tesla to 3.0 Tesla) of about 1-2 ms or less. The MRI signal S in Gradient Echo imaging (GRE) is given by S(TE; T2*)=S_0*EXP(−TE/T2*), where TE is the variable echo time, and S_0 is the signal at a (fictitious) echo time TE=0 ms. On the other hand, most tissues have T2* which are longer than 2 ms, so that the factor EXP(−TE/T2*) for them does not vary much, if TE is varied in the range of 0.5-2 ms, whereas for silicone the signal at a TE_1 of 1-2 ms is much lower as compared to a TE_2 of 0.5 ms or less. Thus, the signal difference

Delta_S=S(TE_1)−S(TE_2)=S_0*(EXP(−TE_1/T2*)−EXP(−TE_2/T2*))

[0047] is non-vanishing for the substrate (e.g., silicone), but it does vanish for brain tissue.

[0048] A marker from substrate material (e.g. silicone) can thus be selectively visualized in a difference image acquired with two different echo times, where one is less than the T2* of the substrate material (e.g., silicone), and the other is of the order or slightly larger than the substrate (silicone) T2*, but still lower than that of normal (brain) tissue.

[0049] Thus, the method comprises the steps of:

[0050] Acquiring at least one first T2-weighted image of a body region comprising the implantable array, and at least one second T2-weighted image of the body region comprising the implantable array;

[0051] the first image being acquired at a first echo time, TE_1, the first echo time being smaller than the transverse relaxation time, T2*, of the substrate material (silicone);

[0052] the second T2-weighted image being acquired at a second echo time, TE_2, the second echo time being selected to be equal to or greater than the transverse relaxation time, T2*, of the substrate material (silicone), but smaller than the transverse relaxation time, T2*, of body tissue;

[0053] generating a difference image on the basis of the at least one second image and the at least one first image.

[0054] The at least one first and second images are acquired on the basis of first and second predetermined Gradient Echo (GRE) sequences.

[0055] Herein, the first sequence and the second sequence comprise identical relaxation time TR, inversion time TI, and flip angle (α) setting.