METHOD FOR DETECTING PULSATILE DYNAMICS OF THE OPTIC NERVE SHEATH, DIAGNOSTIC METHODS, MEDICAL USES, NON-INVASIVE MARKERS, SYSTEMS AND TRANSDUCER DEVICES

Abstract

The invention relates to a new method, as well as diagnosis. A non-invasive marker, systems and equipment are also included.

Claims

1. A method for non-invasively determining a state of at least one marker selected from the group consisting of: a marker indicating possibly increased intracranial pressure of a patient and a marker indicating another condition affecting an optic nerve sheath of the patient, the method comprising: locating the patient's optic nerve sheath; monitoring motion of the optic nerve sheath using at least one of: a transducer device and data recorded with a transducer device, to detect displacements of the optic nerve sheath; using the detected displacements to determine a measure of stiffness of the optic nerve sheath; and using the detected displacements and the measure of stiffness to determine the state of the at least one marker.

2. The method of claim 1, wherein the method is for non-invasively determining the state of a marker indicating possibly increased intracranial pressure of a patient, and wherein increased stiffness is associated with increased intracranial pressure.

3. The method of claim 1, wherein monitoring motion of the optic nerve sheath to detect displacements is carried out over a period of time including one or more cardiac cycles.

4. The method of claim 3, wherein motion of the optic nerve sheath is caused by cardiac and/or respiratory motion in the patient.

5. The method of claim 4, wherein using the detected displacements and the measure of stiffness to determine the state of the at least one marker comprises analysis of variations occurring during a single cardiac cycle.

6. The method of claim 1, comprising detecting the displacements as they vary with time at two locations around the optic nerve sheath or in the region surrounding the optic nerve sheath, wherein determining the measure of stiffness of the optic nerve sheath includes obtaining a parameter of deformability () based on the displacements.

7. The method of claim 6, wherein the parameter of deformability () is calculated according to the equation: $=\frac{.Math.d_A-d_B.Math.}{d_A+d_B}$ wherein d.sub.A and d.sub.B represent the displacements at the two locations.

8. The method of claim 1, further comprising performing a Fourier analysis of a motion pattern of the optic nerve sheath in a direction perpendicular to a longitudinal axis of the optic nerve sheath.

9. The method of claim 1, further comprising inducing a displacement or an associated biological response in order to prompt motion of the optic nerve sheath.

10. The method of claim 1, further comprising obtaining the optic nerve sheath diameter.

11. The method of claim 1, wherein the transducer device comprises an ultrasound transducer, an x-ray emitter, a magnetic resonance imager, a computed tomography scanner, optical coherence tomography scanner, or a combination of any two or more thereof.

12. An apparatus for non-invasively calculating at least one of a marker indicating possibly increased intracranial pressure of a patient and a marker indicating another condition affecting an optic nerve sheath of the patient, the apparatus comprising: an imaging system for locating the optic nerve sheath and for monitoring displacements arising from motion of the optic nerve sheath, the imaging system including at least one of a transducer device and data recorded with a transducer device; and a data analysis device configured to: use the displacements to determine a measure of stiffness of the optic nerve sheath; and use the detected displacements and the measure of stiffness to estimate the state of the marker.

13. The apparatus of claim 12, wherein the apparatus is for non-invasively determining a marker indicating possibly increased intracranial pressure of a patient, and wherein the data analysis device is configured to associate increased stiffness with increased intracranial pressure.

14. The apparatus of claim 12, wherein the imaging system is configured to detect the displacements as they vary with time at two locations around the optic nerve sheath or in the region surrounding the optic nerve sheath, and wherein the data analysis device is configured to obtain a parameter of deformability () based on the displacements.

15. The apparatus of claim 12, wherein the parameter of deformability () is calculated according to the equation: $=\frac{.Math.d_A-d_B.Math.}{d_A+d_B}$ wherein d.sub.A and d.sub.B represent the displacements at the two locations.

16. The apparatus of claim 12, wherein the data analysis device is configured to perform a Fourier analysis of the motion pattern of the optic nerve sheath in a direction perpendicular to a longitudinal axis of the optic nerve sheath.

17. The apparatus of claim 12, wherein the data analysis device is configured to obtain the optic nerve sheath diameter as an augment.

18. The apparatus of claim 12, wherein the transducer device comprises an ultrasound transducer, an x-ray emitter, a magnetic resonance imager, a computed tomography scanner, optical coherence tomography scanner or any combination thereof.

19. A computer program product comprising instructions that, when executed, will configure an apparatus to non-invasively determine at least one of a marker indicating possibly increased intracranial pressure of a patient and a marker indicating another condition affecting an optic nerve sheath of the patient in accordance with the method of claim 1.

20. A method for detecting pulsatile dynamics of an optic nerve sheath (ONS) or in a region surrounding the ONS, comprising the steps of: locating the ONS; choosing one or more locations around the ONS or in the region surrounding the ONS; and measuring the pulsatile dynamics at the one or more locations over a given time period or frequency.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0031] FIG. 1 shows how the optic nerve sheath (ONS) is subject to a modeled net force F due to cardiovascular pulsation (e.g. caused by internal or external arteries, or by pulsations transmitted through the CSF). This force causes a motion d.sub.Left on the left side of the ONS and a motion d.sub.Right on the right side. Raised ICP makes the ONS stiffer, which is observed as more equal radial (r) motion on each side of the ONS.

[0032] FIGS. 2A and 2B illustrate the image processing, with a normal (FIG. 2A) and a high ICP patient (FIG. 2B). Upper row: The white squares show the region of interest used for tracking. Mid row: radial displacement as a function of time (vertical axis) after extraction of the motion component corresponding to the heart rate frequency. Note that the curves are strongly zoomed in compared to the images in the upper row (the squares are 25 pixels wide, pulsation is approx. 0.1 pixel). Lower row: the same curves, plotted together, with displacement amplitude along the vertical axis and time along the horizontal axis. Note the difference in displacements for the normal ICP patient compared to the high ICP patient.

[0033] FIG. 3 is a boxplot illustrating the difference in radial (or transverse) pulsatile deformability (parameter of deformability), , between the two groups. The boxplot shows median, 25- and 75-percentiles and range.

[0034] FIG. 4 represents a receiver operator curve. Area under curve (AUC) was 0.85.

[0035] FIG. 5 shows sensitivity and specificity as a function of . A cutoff of =0.121 gave sensitivity 90% and specificity 87%.

DETAILED DESCRIPTION OF THE INVENTION

[0036] The present invention may be understood more readily by reference to the following detailed description taken in connection with the accompanying figures and example, which form a part of this disclosure. It is to be understood that the present invention is not limited to the specific devices, methods, applications, conditions, systems or parameters described and/or shown herein, and that the terminology used herein is for the purpose of describing particular embodiments by way of example only and is not intended to be limiting of the claimed invention.

[0037] The optic nerve is a bundle of individual axons that in turn connect the retinal ganglion cells to the brain. The optic nerve leaves the posterior of the eye at the scleral canal and travels to the optic chiasm.

[0038] The optic nerve is a second cranial nerve. It is about 5 cm in length, and it starts from the optic disc and extends up to the optic chiasma where the two nerves (from each eye) meet. The optic nerve has 4 parts:

[0039] 1) the intraocular part is approximately 1 mm and it passes through the sclera, choroid and appears in the eye as the optic disc.

[0040] 2) the intraorbital part is 30 mm and extends from the back of the eyeball to the optic foramina.

[0041] 3) the intracanalicular part is 6 mm, and enters the optic canal through the optic foramen.

[0042] 4) the intracranial part is 10 mm, and lies above the cavernous sinus. The optic chiasma is formed just above the sellae.

[0043] Both the intraorbital and the intracanalicular part of the optic nerve is surrounded by 3 layers of meninges; the pia, the arachnoid and dura mater. In contrast, the optic nerve in the cranial cavity is surrounded only by the pia mater. Between the dura and the arachnoid mater, is the subdural space and between arachnoid and pia is the subarachnoid space, both of which are communicating with the corresponding intracranial space.

[0044] The optic nerve sheat, ONS is hereinafter defined as the three layers of meninges; the pia mater, the arachnoid mater and the dura mater, surrounding the intraorbital and intracanalicular part of the optic nerve.

[0045] The intraorbital region is hereinafter defined as the region where the intraorbital part of the optic nerve lays.

[0046] The intracanalicular region is hereinafter defined as the region where the intracanalicular part of the optic nerve lays.

[0047] The optic nerve sheath surrounds the optic nerve, and encloses cerebrospinal fluid (CSF). An increase in cerebrospinal fluid pressure (which is equivalent to intracranial pressure) causes a distention of the optic nerve sheath (ONS).

[0048] According to one embodiment of the method of the invention, the region suitable for detection of the pulsatile dynamics is the ONS and the surrounding region, also known as the intraorbital and/or intracanalicular region

[0049] The inventors have found that the increased intracranial pressure, and subsequent distension in the subarachnoid space, also leads to a stiffer and less compressible nerve sheath. This is due to the fact that the optic nerve sheath (ONS) is a continuation of the intracranial meninges, and the perineural subarachnoid space surrounding the optic nerve is a septated, trabeculated, cerebrospinal fluid (CSF) filled region. This space is in communication with the intracranial compartment, and changes in ICP are therefore transmitted along these CSF pathways. Consequently, as the ICP increases, a buildup of CSF occurs within the perineural space, leading to increased pressure and distension of the ONS. The inventors have found that the buildup of CSF within the perineural space, in addition to lead to the distension of ONS, also changes the dynamic of the optic nerve sheath and the tissue the surrounding regions. This is contrary to prior art which teaches ONS diameter measurement based on the distension as the sole marker of increased ICP. By assessing the dynamics, the inventors have developed a new, reliable method. This method provides an accurate diagnostic tool, useful both in relation to assessing ICP and other condition which affects the optic nerve sheath.

[0050] The invention discloses a method for detecting the pulsatile dynamics of ONS and pulsatile dynamics in tissue in regions surrounding ONS. In particular, the invention discloses a method for detecting pulsatile dynamics of ONS and in the surrounding tissue in the optic canal, such as in the intraorbital region and/or intracanalicular region. Particularly, it is provided a method for detecting the pulsatile dynamics of ONS and in the region surrounding the ONS comprising the step of a) locating the ONS, b) choosing one or more location in the ONS or the intraorbital and/or intracanalicular region surrounding the optic nerve sheath and c) measure the pulsatile dynamic at the location over a given time period or frequency. Alternatively the method comprises the step of a) locating the ONS, b) using a transducer device to detect motion and/or displacement and/or for tissue selected around the optic nerve sheath, c) considering the difference in behaviour for detected motion and/or displacement and/or velocity for one or at least two locations around the ONS,

[0051] The method is particularly useful in order to assess the intracranial pressure, as a relation between ICP and the increased pressure within the subarachnoid space in the ONS is established by this invention. However, assessment of ONS dynamics may also serve as an indicator for other conditions than ICP. Examples can be cancerous tumor in the optic nerve, optic nerve disorders such as optic neuritis or inflammation, glaucoma, ischemic optic neuropathy, or other damage to the optic nerve or surrounding tissue.

[0052] The term pulsatile dynamic as used herein refers to the motion, movement, displacement or changes in velocity, or any parameters derived thereof. As such pulsatile dynamics could mean any relevant dynamic property. While pulsatile indicates that the parameter is preferably related to cyclic behaviour such as that imposed by respiratory or cardiovascular pulsation, the concept should not be understood as limited to cyclic behaviour. The pulsatile nature of the dynamics may be caused directly by the arterial pulsation, or transmission of pulsatility (e.g. variation in pressure) through the CSF. The pulsatility may be caused by the cardiac or respiratory cycles, among other. It is also possible that a periodic alteration of behavior of the optic nerve sheat may be caused by external factors, as for example by applying mechanical or acoustic force.

[0053] The estimated dynamics may be related directly or indirectly to ICP, because of the increased levels of CSF in the perineural space.

[0054] By analyzing this dynamics the inventors were able to show an association with ICP. Thus, they have provided a tool for diagnosing increased levels of ICP. The invention discloses a method for analyzing dynamic properties of the ONS using a transducer device, in particular by using transorbital ultrasound transducer. This method provides an insight into the relationship between ONS dynamics in response to variations in the ICP.

[0055] Specifically, the inventors have found that raised ICP alters the dynamics in or in the region surrounding the ONS, and that this alteration may be detected by studying the motion, movement, displacement or changes in velocity (e.g. the dynamic behaviour) of the ONS or surrounding structures. By using the transducer device the inventors have been able to further investigate this pulsatile dynamics of the ONS over a given time period (e.g. a cardiac cycle).

[0056] The expression a given time period as used herein refers to the length in time of the cardiac cycle, the respiratory cycle or any other time interval, time period or corresponding frequency that is suitable for observation of the dynamics of the ONS and the surrounding tissue, or able to influence the dynamics of the ONS. The pulsatile dynamics may according to the present invention be determined over a period of time corresponding to for example one cardiac cycle. If at least two location surrounding ONS is chosen, the given time period used may be the same or different for each location. That is, measurement for one location may be done in one given time period, and for another location in a later time period.

[0057] The term transducer device as described herein refers to devices comprising an ultrasound transducer, an x-ray emitter, a magnetic resonance imager, a computed tomography scanner, optical coherence tomography scanner or any combination thereof. The transducer device may be used to obtain an image of the optical nerve sheath and the surrounding tissue/structure, making it possible to quantify the pulsatile dynamics of the relevant tissue. Transducer devices also include similar technology to obtain relevant measurements without displaying images.

[0058] The expression in the region surrounding ONS as used herein refers to the ONS nearby tissue or structure surrounding the ONS that is influenced by the increased levels of CSF in the perineural space in the same or similar way as the ONS itself is influenced, or alternatively influenced by the ICP in a comparable fashion. The expressions region surrounding and area surrounding are used interchangeably. The region may be the intraorbital or the intracanalicular region.

[0059] The invention represents a novel approach, which adds insight into the factors involved in alteration of the ONS in response to changes in ICP. As such, the invention is a new method of detecting characteristics related to ICP by obtaining information about movement or displacement of the ONS or the surrounding structure. The movement/displacement/velocity may be collected by B-mode ultrasound or other imaging modalities (e.g., ocular coherance tomography) or by other means known to those skilled in the art.

[0060] The invention includes use of transorbital ultrasound to detect the pulsatile dynamics of the ONS. This quantifiable dynamics may be used as an individual diagnostic marker for increased or decreased ICP.

[0061] The invention is based on the observation that cardiovascular pulsation (i.e. caused directly by arterial pulsation, or transmission of pulsatility through the CSF) leads to motion of the ONS. Based on the observation that the ONS becomes stiffer and less compliant with increasing ICP, the inventors found that the transverse motion (i.e. perpendicular to the ONS) is more equal on each side of the nerve with high ICP compared to normal ICP. As exemplified by the invention, this may be quantified by the absolute difference between the transverse pulsatile displacements on the left and right side of the ONS, normalized by the sum of displacements. Thus, the invention provides a method for quantifying the displacement by calculating the parameter of deformability, :

[00003]$\begin{array}{cc}=\frac{.Math.d_A-d_B.Math.}{d_A+d_B}& \left(1\right)\end{array}$

[0062] The value of this parameter indicates how much the ONS deforms during cardiovascular pulsation, and is therefore interpreted physically as a measure of deformability. The parameter of deformability may also be referred to as the deformability index. The deformability index or parameter of deformability may be calculated based on movement/displacement in the ONS and the surrounding tissue, caused by the increased level of CSF in the perineural space, by various means known to the skilled person.

[0063] Since the ability to deform is inversely related to stiffness, the inventors have found that this parameter is smaller in a high ICP group compared to a normal ICP group. In fact, a significant difference was noted between patient groups with high versus normal ICP, supporting the invention as a relevant non-invasive marker of raised ICP. Thus, the invention discloses a novel non-invasive marker of increased or decreased ICP obtained by measuring the pulsatile dynamics in two locations in the area surrounding the ONS, such as in the intraorbital and/or intracanalicular region. The invention includes a method of measuring transverse pulsatile displacement on both sides of the ONS in these regions. Increased ICP leads to increased stiffness (i.e. reduced deformability) of the nerve sheath, thus making an objective and quantifiable new approach for assessing variations in ICP.

[0064] The parameter of deformability may be derived from analyses of the dynamic behavior of ONS or surrounding tissue within a given time interval, that may be used for assessing ICP. The dynamic information may also be combined in different ways, and is not restricted to the derivations in Eq. 1.

[0065] The term locations as used herein refers to points or region-of-interest (ROI) of any shape and size in the area surrounding the ONS. In Eq. 1 these locations are represented by d.sub.A and d.sub.B. The terms point, location and region of interest are used interchangeably. In the example and figures enclosed in this description, d.sub.A is sometimes also denoted d.sub.Left, and d.sub.B is sometimes also denoted d.sub.Right

[0066] The term assessing ICP, as used herein, refers to the detection or determination or monitoring of both increased or decreased and normal levels of intracranial pressure. It also includes the method of (continuously) monitoring the ICP levels, and thus detecting potential changes in the ICP.

[0067] The most important finding in this study is the significant difference between the deformability of the ONS in the group with high ICP compared to the group with normal ICP, thus clearly supporting the technical effect of the invention. This finding may be applied in all cases where ONS dynamics are quantifiably changed in response to variations in the ICP, indifferent on the method used to quantify it. An element of importance is that the improvement provided by the present invention compared to the prior art lays in the observation that the natural biovariation of the ONS dynamics between individuals in the different patient groups is less than that observed in mere diameter analysis.

[0068] Thus the invention includes a method for analyzing dynamic properties of the ONS using a transducer device. Further a method of detecting ONS dynamics in response to ICP and/or variations in the ICP is provided. A method of detecting variations in the ICP by continuously measuring the pulsatile dynamics of the ONS is accordingly also provided.

[0069] The motion/displacement/velocity in tissue selected around the optic nerve sheath may be detected in any given direction, whether it is transvers motion perpendicular to the ONS or it is motion or displacement detectable longitudinal to the ONS, or any other direction.

[0070] In the past the non-invasive assessment of ICP has been dependent of the ONS diameter measurement. This method is highly unreliable. It has been considerably variation in the optimal cutoff point for the ONSD measurement. The noted variation in ONSD between studies is likely due to a more complex relationship between the ONS and ICP. The magnitude of ONS distension caused by the increase in pressure within the subarachnoid space is dependent on a variety of factors, including the degree to which ICP is increased, the rapidity of the increase in ICP and the elastic characteristics of the ONS. All these factors influence the capability for distension and retraction of the ONS. In addition, the relationship between ONSD and ICP is not known for every individual case. This is because of natural biovariation between individuals in normal optic nerve diameter and in tissue mechanical elasticity. Naturally ONS diameter measurements alone do not provide reliable estimates of ICP. The invention is thus also useful as an augment to the interpretation of the more familiar ONS diameter measurement. In their study, the inventors have found that the pulsatile forces from the beating of the heart deform the ONS dynamically during the cardiac cycle. This is in contrast to the former absolute distention related to the increased pressure within the ONS. By using a transducer device over the oculus, the invention as described herein may be used complementary to the static measurements of ONSD.

[0071] By using an imaging transducer device it is possible to combine the information from analysis of pulsatile dynamics and diameter of the ONS. Thus the combined information, which may be obtained during the same examination as presented by this invention, represents an improvement of the overall accuracy and reliability of examining the ONS as a non-invasive marker of ICP.

[0072] Thus the new approach provides additional information complementary to the ONSD. The invention contributes to an overall improvement in assessing the ONS in cases of suspected increased ICP, both as an individual marker and by augmenting the interpretation of ONSD measurements. The concept of pulsatile dynamics of the ONS, obtainable by using the method as described herein, thus improve the specificity compared to ONSD alone, making it possible to differentiate between pathologically distended ONS due to raised ICP and widened ONS not related to raised ICP.

[0073] The invention also includes the analysis of additional information, e.g. longitudinal motion or phase content of the Fourier transform (e.g. delay between motions at different location around the nerve). It is also possible to apply the herein described method in relation to other motion components than the fundamental heart rate frequency. In addition to higher harmonics of the cardiac frequency, respiration is an example of another physiological process that causes a periodic motion in the body tissues. Motion or dynamics, preferably but not limited to pulsatile or periodic of nature, might also be applied by the use of externally applied mechanical or acoustic force of any magnitude, or artificially induced as a response to other stimuli, e.g. medication, or electrical or audiovisual impulses.

[0074] The invention include a method for assessment of intracranial pressure, or any parameters related to intracranial pressure, in particular comprising the step of transmitting ultrasound through the oculus using an adequate transducer and ultrasound scanner and calculation of motion in the ultrasound data (preferable selected around the oculus and optic nerve sheet complex). Further the method according to the present invention is analysing the spectrum of the calculated motion that has occurred during the given time period by doing Fourier analysis of the motion pattern in any given direction. The invention uses the characteristics of the spectral component of the motion for any one or at least two region of interests to derive a parameter, such as the parameter of deformability.

[0075] Also disclosed are a method of non-invasively monitoring ICP, comprising the step of locating the ONS, using an imaging device, like for instance transorbital ultrasound, to detect motion/displacement/velocity for tissue selected around the optic nerve sheath, considering the difference in behaviour for detected motion/displacement/velocity for one or at least two locations or regions of interests, in order to assess the intracranial pressure.

[0076] The invention uses a transducer to investigate the pulsatile dynamics of the ONS over a cardiac cycle.

[0077] The invention discloses a method for assessment of ONS pulsatile dynamics using transorbital ultrasound imaging.

[0078] The invention is a novel method for analyzing the pulsatile dynamic properties of the ONS using transorbital ultrasound imaging.

[0079] The invention include any method for estimating parameter(s) related to displacement/motion at the heart beat frequency or period, or any other that is occurring during any time sequence and any spectral component for one or at least two different regions of interests in the acquired ultrasound data. The region of interest (ROI) can be of any given size.

[0080] The invention is a novel method for extracting dynamic characteristics (e.g. pulsatile motion) of the optic nerve sheath or nearby structures, for the purpose of assessing intracranial pressure. According to the method the pulsatile dynamic is measured based on the detection of motion or velocity from data obtained from the transducer device. The method comprises the step of obtaining dynamic measurements of ROI in or close to the ONS by e.g imaging, such as ultrasound, tracking and/or estimating motion (e.g. alternatively crosscorrelation), extracting different motion components, such as e.g. perpendicular to the ONS, on both sides of the ONS, with or without need for filtering to enhance relevant (here: pulsatile->cardiovascular) motion, e.g. extracting motion corresponding to heart-rate frequency and relating the motion to ICP by using the parameter of deformability. The present invention also provides devices to be applied in such a method. In one embodiment the device includes an imaging component configured to obtain an image of the optic nerve sheath and the related tissue, and based on the detected motion in this region of interest produce an assessment of the ONS deformation during the cardiovascular pulsation.

[0081] FIG. 1 illustrates that the optic nerve sheath (ONS) is subject to a modeled net force F due to cardiovascular pulsation (e.g. caused by internal or external arteries, or by pulsations transmitted through the CSF). This force causes a motion d.sub.Left on the left side of the ONS and a motion d.sub.Right on the right side. Raised ICP makes the ONS stiffer, which is observed as a more equal radial motion on each side of the ONS.

[0082] FIGS. 2A and 2B illustrate the image processing, with a normal FIG. 2A and a high ICP patient FIG. 2B. Upper row: The white squares show the region of interest used for tracking. Mid row: radial displacement as a function of time (vertical axis) after extraction of the motion component corresponding to the heart rate frequency. Note that the curves are strongly zoomed in compared to the images in the upper row (the squares are 25 pixels wide, pulsation is approx. 0.1 pixel). Lower row: the same curves, plotted together, with displacement amplitude along the vertical axis and time along the horizontal axis. Note the difference in displacements for the normal ICP patient compared to the high ICP patient.

[0083] FIG. 3 is a boxplot illustrating the difference in radial (or transverse) pulsatile deformability (parameter of deformability), A between the two groups. The boxplot shows median, 25- and 75-percentiles and range.

[0084] FIG. 4 shows receiver operator curve. Area under curve (AUC) was 0.85.

[0085] FIG. 5 shows sensitivity and specificity as a function of . A cutoff of =0.121 gave sensitivity 90% and specificity 87%.

Example 1

Patients

[0086] We performed an exploratory research study, retrospectively analyzing data from 16 patients (age 12 years old), managed at the Red Cross War Memorial Children's Hospital (Cape Town, South Africa). Inclusion criteria were that: 1) invasive ICP measurement, via insertion of a parenchymal microsensor or a ventricular catheter, was performed during a diagnostic or therapeutic intervention, and 2) concurrent transorbital ultrasound images of the ONS were acquired. Patients with ocular pathology were excluded. The human research ethics committee of the University of Cape Town and the research committee of the Red Cross War Memorial Children's Hospital approved the study, and informed consent was obtained for all patients enrolled in the study. The demographic details are listed in Table I.

Table I. Demographic Data.

[0087]

TABLE-US-00001 TABLE I Demographic data. Age Heart rate ICP Patient (months) Gender (bpm) Diagnosis (mmHg) Group A 120 M 78 Posterior fossa Tumor 28 High B 116 F 103 Hydrocephalus 33 High C 132 M 168 Trauma 32 High D 33 M 117 Posterior fossa Tumor 37 High E 24 F 92 Hemispheral tumor 20 High F 124 F 112 Hydrocephalus 30 High G 38 F 69 Hydrocephalus 26 High H 44 M 134 Hydrocephalus 36 High I 36 M 100 Tethered cord 10 Normal J 9 M 150 Hydrocephalus 8 Normal K 72 F 92 Chiari1 malformation 5 Normal L 54 M 102 Spinal dysraphism 10 Normal M 144 M 80 Hydrocephalus 10 Normal N 10 M 120 Hydrocephalus 11 Normal O 8 M 130 Hydrocephalus 10 Normal P 94 M 103 Trauma 10 Normal

Image Acquisition

[0088] A single investigator experienced in the use of transorbital ultrasonography acquired ultrasound images from both eyes, using a 15 MHz linear array probe (L15-7io, Philips, Bothell, USA). The images were acquired after the patients were intubated and ventilated, just prior to insertion of the invasive ICP monitor. The heart rate was recorded, and ultrasound acquisition was performed when the hemodynamic parameters were stable. The image depth varied from 3 to 5 cm, and spatial image resolution from 0.06 to 0.11 mm per pixel. The duration of each image sequence was 5 to 10 seconds, and the temporal resolution varied from 40 to 56 frames per second.

Image Processing

[0089] The objective of the image processing was to exploit the high temporal resolution of the ultrasound images for analyzing motion related to cardiovascular pulsation on each side of the optic nerve sheath. The approach is explained in FIG. 2, and in the following text.

[0090] 1st Step: Tracking

[0091] Tracking was initialized by manually selecting a point at similar depths on both sides of the ONS in the first frame of each image sequence. The motion was then automatically tracked over the entire sequence using normalized two-dimensional cross-correlation from frame to frame for a region of interest (25 by 61 pixels) around the selected points. The ultrasound data were interpolated, and parabolic approximation was applied to the correlation matrix for sub-pixel motion estimation. The motion component in the horizontal image direction (i.e. radial, or perpendicular, to the nerve) was extracted for further analysis.

[0092] 2.sup.nd Step: Fourier Analysis

[0093] To extract the motion that was related to the cardiovascular pulsation, we applied Fourier analysis to obtain the frequency components of the radial motion. The amplitude of the (fundamental) frequency component corresponding to the heart rate of each patient was extracted for the left and right side of the ONS in each dataset, yielding the radial pulsatile displacements d.sub.Left and d.sub.Right, respectively.

[0094] The algorithm was implemented in Matlab (MathWorks, Natick, Mass., USA).

Data Analysis and Statistics

[0095] Since the data were retrospectively analyzed, we expected some out-of-plane motion, which is known to deteriorate correlation-based tracking. Each dataset were therefore graded by one blinded operator on a scale from 0-2: [0096] Grade 0: steady acquisition, barely perceivable probe movement [0097] Grade 1: perceivable probe motion, no loss of ONS appearance [0098] Grade 2: distinct probe movement, with some loss of ONS appearance

[0099] Seven datasets scoring grade 2 were excluded, leaving 25 for further analysis.

[0100] The motion analysis was run five times for the left and right side of the optic nerve sheath for each dataset to account for variability due to the manual initialization of the tracking region. The mean of the five displacement values was used as the motion estimate, and the variation was quantified using pooled standard deviation.

[0101] The 25 datasets were split into a high ICP group (20 mmHg), and a normal ICP group (<20 mmHg), comprising 10 and 15 datasets, respectively. A was calculated using equation (1), and one-sided Mann-Whitney U-test was used to statistically compare the two groups. Diagnostic accuracy was investigated using receiver operating characteristic (ROC).

Results

[0102] A total of 25 datasets were analyzed. The radial pulsatile displacement at each side of the ONS was assessed five times for each dataset. The mean displacement was 8.3, with a pooled standard deviation of 0.54, measured in percentage of a pixel.

[0103] The radial pulsatile deformability (parameter of deformability) was calculated for each dataset. The median was =0.11 for the high ICP group, compared to =0.24 for the normal ICP group (p=0.002). FIG. 3 shows a boxplot illustrating the median and spread for each group. Results for each patient are included in Table II.

TABLE-US-00002 TABLE II Results. Datasets with out-of-plane motion given a grade 2 were excluded from the analysis. Radial displacements d.sub.Left and d.sub.Right were measured in percentage of a pixel. Left eye Right eye d.sub.Left d.sub.Right Grade d.sub.Left d.sub.Right Grade High ICP A 2 2 group B 7.76 8.75 0.06 1 9.88 9.23 0.03 1 C 2 2.73 3.42 0.11 1 D 5.17 4.17 0.11 1 2 E 15.37 13.58 0.06 0 13.74 17.44 0.12 1 F 20.49 26.12 0.12 1 2 G 2 11.22 9.79 0.07 1 H 6.76 5.37 0.11 1 3.51 5.97 0.26* 0 Normal ICP I 5.65 3.16 0.28 0 2.52 3.78 0.20 0 group J 4.01 1.83 0.37 1 5.70 3.63 0.22 0 K 13.68 8.38 0.24 1 7.22 3.04 0.41 0 L 7.98 4.60 0.27 1 9.12 11.78 0.13 0 M 17.47 10.64 0.24 0 2 N 5.20 3.62 0.18 0 1.52 5.69 0.58 1 O 15.94 16.83 0.03* 1 8.15 3.96 0.35 0 P 4.90 5.61 0.07* 0 5.52 10.32 0.30 1 *Values that are wrongly classified using a cut-off value of 0.121.

[0104] ROC analysis gave an area under curve (AUC) of 0.85 (95% CI: 0.61-0.97) (FIG. 4). FIG. 5 shows the sensitivity and specificity as a function of the parameter . Choosing a cut-off value at =0.121 would give a sensitivity of 90% and a specificity of 87%. 3 out of 25 (12%) datasets would be wrongly classified using this cut-off.

Conclusion

[0105] Example 1 illustrates the feasibility of non-invasive transorbital ultrasound for assessing optic nerve sheath pulsatile dynamics. The results demonstrate a significant difference between patient groups with high versus normal ICP, and thus support the technical effect of the invention. The inventors are the first to explore the relationship between radial pulsatile deformability (parameter of deformability) and intracranial pressure. The invention is relevant as a non-invasive marker of increased or decreased ICP, and may also serve to augment the interpretation of static ONSD measurement.

Example 2

[0106] A handheld transducer device, able to transmit and receive ultrasound is used to perform the method according to the present invention. The handheld device is placed in a suitable position for sonification of the ONS. The device is able to processes the received ultrasound to obtain information about the dynamics of the ONS or surrounding structures, and calculates a parameter of deformability based on the ONS dynamics. The dynamics is related to ICP. The result is then presented either as an image, curve or number on a display, or by other indicators such as sound or light signals. The parameter may in addition be a function including other physiological information, such as the diameter of the ONS or hemodynamic information.

Example 3

[0107] It is possible to measure the dynamics in only one location. The dynamics is then related to a reference value. Optionally the dynamics may also be related to some physiological parameters, e.g. blood pressure, or ECG. Without being bound by theory, it is assumed that higher (intracranial) pressure gives a faster transmission of (cardiovascular) pressure pulses, which could be observed as a smaller time delay between ECG and pulsatile displacement. This time delay could be measured as the phase difference in a cross-correlation between the ECG and the displacement obtained using the described methodology.

REFERENCES

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[0117] WO 02/43564 A1