A position determining system and method

Abstract: A patient's head is anchored ( 16 ) at one end of a patient support ( 10 ). An array of receivers ( 50 ) are mounted on a frame ( 12 ) which is fixed to the patient support. The frame carries at least one reference transmitter ( 52 ). A wand ( 42 ) has at least two emitters ( 44 , 46 )mounted thereto. By measuring relative travel time of the signals from the wand emitters to the receiver array and comparing the travel time with travel time over a known distance from the reference transmitter to one or more of the receivers, the position of the wand in a coordinate system of the patient support is determined ( 80 ). A three-dimensional array of diagnostic image data was taken through the anchored portion of the patient and at least three markers ( 114 ) affixed to the patient. By positioning the wand on the markers after the patient is secured to the patient support, a transform ( 110 ) between the patient support coordinate system and the image data coordinate system is derived. Once the relationship between the coordinate systems is known, the surgeon can use the wand to select locations and orientations on a surface of the patient and retrieve corresponding portions of the image data for display on video monitors ( 30 ).

Description: This invention relates to a position determining system and method. It finds particular application in conjunction with neurosurgery and will be described with particular reference thereto. However, it is to be appreciated, that the invention will also find application in conjunction with other medical procedures, industrial quality control procedures, and the like. Three-dimensional diagnostic image data of the brain and other body portions are commonly available with CT scanners, magnetic resonance images, and other medical diagnostic equipment. These imaging modalities provide structural detail with a resolution of a millimetre or better. Various stereotaxy procedures have been developed which require extreme accuracy. Typical neurosurgical procedures included guided-needle biopsies, shunt placements, craniotomies for lesion or tumour resection, and the like. A three-dimensional "localizer" is attached to the patient's skull. The localizer is a mechanical device with precisely known geometry and dimensions for guiding or positioning surgical instruments. The localizer is commonly attached to a ring or frame of metal or plastic from which the name "framed" stereotaxy has evolved. This frame is typically affixed to the patient using various mounting hardware methods that include sharp points or pins that pierce the skin and locate into the skull. The localizer is then mounted onto a frame. The localizer and frame provide the surgeon with the ability to position surgical instruments mechanically with a mechanical accuracy of a millimetre or better. However, anatomically, accuracy is somewhat less due to inaccuracies in the diagnostic imaging and patient motion. One of the difficulties that has arisen is accurately coordinating the coordinate system of the patient's skull or stereotaxy localizer with the coordinate system of the diagnostic data. One solution has been to image the patient with the stereotaxic frame attached. Because the stereotaxic frame appears in the resultant images, the surgeon is provided with a frame of reference in the images. Although relatively accurate in coordinating the two frames of reference, the use of the frame has numerous drawbacks including the need to mount the frame to the patient's head for both the imaging and the surgical procedures and the associated cost. A frameless position determining system is know from document IEEE Transactions on biomedical engineering, vol.36, no.6, June 1989, New York, US, pages 608-617. This document discloses to coordinate the coordinate system of the patient's skull with the coordinate system of the diagnostic data by placing a sound emitter on marks on the patient's skull and detecting their respective positions by three receivers. According to a first aspect of the present invention there is provided a position determining system comprising: a subject support; a means for securing a preselected portion of a subject to the subject support; a frame assembly which mounts at least three receivers in a fixed relationship to the subject support closely adjacent the means for securing a portion of the subject to the subject support; at least one reference emitter mounted a fixed, known distance from the receivers, the reference emitter emitting a reference signal which travels from the reference emitter the fixed distance to the receivers; a calibration means for measuring a reference travel time of the reference signal over the fixed distance; a wand having a pointer and at least two emitters mounted thereto, the two wand emitters selectively emitting wand signals which are received by the at least three receivers; a wand position determining means for determining a position of the wand pointer by measuring wand signal travel times of the wand signals between the two wand emitters and the at least three receivers, the wand position determining means being connected with the calibration means for calibrating the wand signal travel times with the reference travel time. According to a second aspect of the present invention there is provided a position determining method comprising: a) securing a portion of a subject to a subject supporting surface in close proximity to at least three signal receivers that are mounted in a fixed relationship to the subject supporting surface; b) positioning a wand to designate selected locations on the subject portion, the wand having at least two wand emitters mounted thereon for selectively emitting signals which are received by the receivers; c) actuating the wand emitters to emit wand signals; d) from the wand emitter signals, calculating coordinates of the wand emitters in a coordinate system of the subject support; e) comparing a calculated distance between calculated wand emitter coordinates and a physical distance between the wand emitters; f) in response to the difference between the calculated distance and the physical distance exceeding a preselected standard, providing an unacceptable measurement signal. According to a third aspect of the present invention there is provided a position determining method comprising: a) securing a portion of a subject to a subject supporting surface in close proximity to at least three signal receivers that are mounted in a fixed relationship to the subject supporting surface, a reference signal emitter being fixedly mounted at a fixed, known distance from the plurality of receivers; b) positioning a wand to designate selected locations on the subject portion, the wand having at least two wand emitters mounted thereon for selectively emitting signals which are received by the receivers; c) actuating the wand emitters individually and the reference emitter in close temporal proximity to emit wand and reference signals; d) measuring travel durations for the wand and reference signals to travel from each of the wand emitters to the receivers and from the reference emitter to the receivers; e) from the travel times, calculating coordinates of the locations designated by the wand in a coordinate system of the subject support. One advantage of an apparatus and method embodying the present invention is that it provides a technique which simply and painlessly coordinates the coordinate system of three-dimensional image data obtained from one or more imaging modalities with the coordinate system of the patient prior to or during surgery. Another advantage of an apparatus and method embodying the present invention is that no frame is needed during the image acquisition scan. Another advantage of an apparatus and method embodying the present invention is that sterilization of necessary parts of the system is facilitated. Another advantage of an apparatus and method embodying the present invention is that it is easy to use and very user friendly. An apparatus and method in accordance with the present invention will now be described, by way of example, with reference to the accompanying drawings in which: FIGURE 1A is a perspective view of an operating room in which the present invention is deployed; FIGURE 1B is a block diagram of the image data manipulation of the system of FIGURE 1A; FIGURES 2A, 2B AND 2C illustrate the wand of FIGURES 1A AND 1B; FIGURE 3 is a detailed illustration of the locator assembly of FIGURE 1; FIGURE 4 is a diagrammatic illustration of a calibration procedure; FIGURES 5A AND 5B are diagrammatic illustrations of the wand and locator relationship; FIGURE 5C is a flow diagram of the wand location procedure; FIGURES 6A, 6B, 6C and 6D are illustrative of a coordinate transform between the coordinate system of the data and the patient. With reference to FIGURE 1A, a subject, such as a human patient, is received on an operating table or other subject support 10 and appropriately positioned within the operating room. A frame 12 is fixed to the patient support such that it is precisely positioned within the subject or subject support coordinate system. Mounting the frame 12 to the patient support permits the patient support to be turned, raised, lowered, wheeled to another location, or the like, without altering the patient coordinate system. The frame 12 supports a plurality of emitter/receiver combinations 14 mounted at fixed, known locations thereon. Preferably, a head clamp 16 or other means securely positions the patient's head or other portion of the subject under consideration in the subject support coordinate system. The frame is mounted at a fixed or selectable angle from vertical such that the frame is positionable more toward the patient, yet still focusing on the region of interest of the patient. With continuing reference to FIGURE 1A and further reference to FIGURE 1B, an operator console 18 houses a computer system 20 . Alternately, the computer system can be remotely located and connected with the control console 18 by cabling. The computer system includes a three-dimensional data memory 22 . The stored three-dimensional image data preferably contains a video pixel value for each voxel or point in a three-dimensional rectangular grid of points, preferably a 256 x 256 x 256 grid. When each image value represents one millimeter cube, the image data represents about a 25.6 centimeter cube through the patient with one millimeter resolution. Because the data is in a three-dimensional rectangular grid, selectable orthogonal and other oblique planes of the data can readily be withdrawn from the three-dimensional memory using conventional technology. A plane selecting means 24 selects various two-dimensional planes of pixel values from the three-dimensional memory for display. In the preferred embodiment, the plane selecting means selects at least three planes: axial, sagittal, coronal, and oblique planes through a selectable point of the patient. The pixel values which lie on the selected axial, sagittal, coronal, and oblique planes are copied into corresponding image memories 26a , 26b , 26c , and 26d . A video processor means 28 converts the two-dimensional digital image representations from one or more of image memories 26 into appropriate signals for display on video monitors 30 or other appropriate display means. With continuing reference to FIGURE 1A and further reference to FIGURE 2A, in order to designate a position on the patient, the surgeon positions a tip 40 of a wand 42 at the desired location. The locator system locates the coordinate of the tip and the trajectory of the wand. More specifically, the wand includes a pair of emitters 44 and 46 which selectively emit positioning signals, ultrasonic signals in the preferred embodiment. With reference to FIGURE 2B, the first emitter 44 has a fixed, known distance ℓ 1 from the tip 40 and the second emitter has a fixed, known distance ℓ 2 from the first emitter 44 . The wand is readily sterilized by conventional techniques. For simplicity of mathematical calculation, the two emitters and the tip are preferably in linear alignment. Optionally, as illustrated in FIGURE 2C, the wand 42 may have a jog 48 which enables the tip and the two emitters to be disposed along a central axis or pointing direction of the wand. With reference to FIGURE 3, the frame 12 includes not only the plurality of receivers, e.g. microphones 50 in the preferred ultrasonic embodiment, but also a plurality of reference emitters 52 . The reference receivers are each spaced along side edges of the frame from adjacent receivers or microphones 50 by distances S 1 and S 2 . Preferably S 1 =S 2 =S . Each reference receiver is also spaced by a distance D across the frame from an oppositely disposed emitter 52 . The emitters and the microphones are normally not coplanar with the frame 12 . Preferably, both distances or range values D are equal in length. In the preferred embodiment, the distance from the wand emitters to the frame, hence the position of the wand relative to the patient, is determined by the travel time of the sound. The velocity of the sound pulse through air is dependent upon both the temperature, the humidity, and the chemical composition of the air. These factors can and do vary significantly during an operation and from procedure to procedure. As shown in FIGURE 4, a calculation is performed to determine the speed of sound in the operating room. More specifically, a calibrating means 60 selectively pulses the reference emitters 52 , receives the signals at receivers 50 , and processes the elapsed time information in accordance with the procedure of FIGURE 4. More specifically, the calibration means 60 includes a step or means 62 for causing a first of the reference emitters 50 to emit a signal pulse. A step or means 64 acquires the range values D', i.e. the time required for the ultrasonic pulses to traverse the distance D. A step or means 66 causes this procedure to be repeated a preselected number of times, such as once for each of the four emitters illustrated in FIGURE 3. Once the travel time between each emitter and receiver pair has been obtained a preselected number of times, a step or means 70 corrects the times for fixed machine delays. That is, there is a fixed, small delay between the time when the command is given to fire the reference emitters 52 and the time that they actually produce a detectable ultrasonic signal. Analogously, there is a small delay between the time that the ultrasonic pulses reach the receiver or microphone 50 and the time that it becomes a measurable electrical signal received by the computer processor. These delays are subtracted from the times measured by step or means 64 . An averaging means 72 averages the actual times after correction for the machine delays for transmission of the ultrasonic pulse between the transmitter and receiver. The time over the range values D' provide the most accurate results. A step or means 74 computes a calibration factor F indicative of the current speed of the ultrasound signal adjacent the patient in the operating room. In the preferred embodiment, the calibration factor F is a ratio of the sonically measured distance D' versus a precise mechanical measurement of the distance D. With reference to FIGURES 5A, 5B, and 5C, a wand coordinate and trajectory determining means 80 determines the position of the two emitters 44 and 46 , respectively. More specifically, a step or means 82 causes the emitter 44 to emit an ultrasonic signal. The receivers 50 on the frame 12 receive the ultrasonic signal at corresponding times L 1 -L 4 . A step or means 84 acquires and retains these times. A step or means 86 causes the second emitter 46 to transmit. A step or means 88 acquires the four times L 1 -L 4 which are required for the ultrasonic signals to pass from the second emitter to the microphones 50 . The speed of ultrasonic transmission and accuracy of transmission times are such that these distances can be measured to within a millimeter or better. A step or means 90 causes the emitters to emit and corresponding data values L 1 -L 4 to be acquired each of a plurality of times to improve digitation accuracy, e.g. two times. A step or means 92 causes the calibration means 60 to perform the steps described in conjunction with FIGURE 4 in order to provide a current indication of the velocity of sound adjacent the patient. Of course, the calibration procedure of FIGURE 4 may be performed immediately before steps 82-88 or intermittently during the collection of several data values for averaging. A step or means 94 corrects the values values L 1 -L 4 for the fixed machine delay discussed above in conjunction with step or means 70 . A step or means 96 corrects each of the times L 1 -L 4 that were required for the ultrasonic signals to travel from the first and second emitters 44 , 46 to the microphones 50 in accordance with the correction factor F determined by step or means 74 . An averaging means 98 averages the delay and calibration corrected times L 1 -L 4 , hence distances between each of the wand emitters 44 , 46 and each of the microphones 50 . From these distances, provided at least three receivers 50 are provided, a step or means 100 calculates the Cartesian coordinates (x 1 ,y 1 ,z 1 ) and (x 2 ,y 2 ,z 2 ) in the patient space for the two emitters 44 and 46 . The first emitter coordinates x 1 ,y 1 ,z 1 are calculated from three of the four range values L 1 -L 4 . With L 4 disregarded, the coordinates are calculated as follows: x 1 = [(L 1 2 -L 2 2 )+S 2 ]/2S y 1 = [(L 1 2 -L 3 2 )+S 2 ]/2S z 1 = [L 1 2 -x 1 2 -y 1 2 ] 1/2 where S=S 1 =S 2 as defined in FIGURE 3. Preferably, the three selected range values are the three shortest of L 1 -L 4 . Similar computations are calculated for x 2 , y 2 , and z 2 coordinates of the second emitter. A step or means 102 checks the validity of the measurement. More specifically, the known separation between the wand emitters is compared with the separation between the measured coordinates x 1 y 1 ,z 1 and x 2 ,y 2 ,z 2 of the wand emitters, i.e.: |Sep known -[(x 1 -x 2 ) 2 +(y 1 -y 2 ) 2 +(z 1 -z 2 ) 2 ] 1/2 | ≤ error If the difference between the measured and known separations is greater than the acceptable error, e.g. 0.75 mm when measuring with a resolution of 1 mm, an erroneous measurement signal is given. The measurement is discarded and the surgeon or other user is flagged to perform the measurement process 80 again. A step or means 104 from the coordinates of the two emitters 44 , 46 , and from the geometry of the wand discussed in FIGURE 2, calculates the Cartesian coordinates (x 0 ,y 0 ,z 0 ) for the wad tip 40 . The tip coordinates x 0 , y 0 , z 0 are defined by: r = ℓ 1 /ℓ 2 x 0 = (1+r)x 1 -rx 2 y 0 = (1+r)y 1 -ry 2 z 0 = (1+r)z 1 -rz 2 With reference to FIGURE 6, a transform means 110 transforms the coordinates of patient space into the coordinate system of the image data and vice versa. More specifically, prior to the imaging, three or more fiducials or markers are affixed at three or more spaced points on the patient's head. The fiducials are visible in the imaging medium selected such that they show up as readily identifiable dots 112 in the resultant image data. In thepreferred embodiment, the fiducials are markers or small beads 114 that are injected with radiation opaque and magnetic resonance excitable materials. A small dot or tattoo is made on the patient's skin and a fiducial is glued to each dot. This enables the position of the fiducials to be denoted even if the fiducials are removed in the interval between the collection of the image data and the surgical procedure. Alternately, portions of the markers can be portions of the patient's anatomy which are readily identifiable in both patient and image space, e.g. the tip of the nose. To align the images of the fiducials with the fiducial positions in patient space, the tip of the wand is placed on each fiducial or tattooed marker point. The coordinates in patient space of each fiducial are determined with the procedure described in conjunction with FIGURES 5A-5C. The position of the three or more fiducials on the patient's scalp are compared with the relative position of the pixels 112 in the image space. The patient space coordinates of marks 114 on the patient's skull in the coordinate system of the patient support are measured. A like coordinate system through the pixels 112 is defined and compared to the patient space coordinate system. The translation and rotational relationship between image space and patient space coordinate systems is determined. With reference to FIGURE 6A, the position of the patient in operating room space (x,y,z) and the relative position in image space (x',y',z') are determined. That is, two coordinate systems are defined. The translation means first determines the offset x offset , y offset , z offset between the barycenters 116 , 118 of the triangles defined by the coordinates of three fiducials in data and patient space, respectively. This provides a translation or an offset in the x, y, and z-directions between the two coordinate systems. The values of x offset , y offset , and z offset are added or subtracted to the coordinates of the patient space and the coordinates of image space, respectively, to translate between the two. With reference to FIGURE 6B, translating the origins of the two coordinate systems into alignment, however, is not the complete correction. Rather, the coordinate systems are normally also rotated relative to each other about all three axes whose origin is at the barycenter. As illustrated in FIGURES 6B, 6C, and 6D, the angle of rotation in the (y,z), (x,z), and (x,y) planes are determined. Having made these determinations, it is a simple matter to transform the patient support space coordinates into the image space coordinates and, conversely, to rotate the image space coordinates into patient space coordinates. The wand coordinate means 80 is connected through the transform means 110 with one of the plane selecting means 24 and the video processor 28 to cause a marker, e.g. cross hairs, to be displayed on the monitors 30 at the coordinates of the wand tip. This enables the surgeon to coordinate specific points on the patient or in the incision with the images. Having aligned the data and patient coordinate systems, numerous techniques can be performed in addition to surgery planning and verification. One can denote two locations in the patient and have them displayed on the monitor in data space. Because the measurement scale in data space is fixed, the distance between the two points is readily determined. The wand can be used to denote points on the patient and mark corresponding points in data space. The marked points can denote electrode locations for example. The present system can be used for out-patient procedures, examinations, and the like, of various parts of the patient's anatomy. Further, more than one set of diagnostic data can be coordinated with the patient. Optionally, an additional three-dimensional data memory 22 ' may store additional diagnostic data, e.g. from another modality, from the same modality, but at different time or with different imaging characteristics, or the like. Once both sets of diagnostic data are coordinated with the patient coordinate system, they are coordinated with each other.

Claims: A position determining system comprising: a subject support (10); a means (16) for securing a preselected portion of a subject to the subject support(10); a frame assembly (12) which mounts at least three receivers (50) in a fixed relationship to the subject support (10) closely adjacent the means (16) for securing a portion of the subject to the subject support(10); at least one reference emitter (52) mounted a fixed, known distance from the receivers (50), the reference emitter (52) emitting a reference signal which travels from the reference emitter (52) the fixed distance to the receivers(50); a calibration means (60) for measuring a reference travel time of the reference signal over the fixed distance; a wand (42) having a pointer(40) and at least two emitters (44,46) mounted thereto, the two wand emitters (44,46) selectively emitting wand signals which are received by the at least three receivers(50); a wand position determining means (80) for determining a position of the wand pointer (40) by measuring wand signal travel times of the wand signals between the two wand emitters (44,46) and the at least three receivers (50), the wand position determining means (80) being connected with the calibration means (60) for calibrating the wand signal travel times with the reference travel time. A system according to claim 1 further including: a three-dimensional image memory means for storing image data indicative of a three-dimensional region of the portion of the subject which is secured to the subject support means; a plane selecting means for selecting planar slices of data from the three-dimensional, image memory means; a display means for converting the selected slices of data from the plane selecting means into human-readable displays; a transform means for transforming a position of the wand pointer into a coordinate system of the image data stored in the three-dimensional image memory means, the transform means being operatively connected with the plane selecting means such that the displayed images have a preselected relationship to the position of the wand pointer. A system according to claim 2 wherein the frame assembly is mounted directly to the subject support to be movable therewith such that movement of the subject support does not alter the subject coordinate system. A system according to claim 2 wherein the frame assembly is mounted to the subject support angled from a perpendicular relationship to focus on the secured subject region, even when mounted away from the secured region of the subject. A system according to claim 2 wherein the subject is a human patient. A system according to claim 2 further including: at least three markers disposed on the selected subject portion, the markers having been secured to the subject when the three-dimensional image data was acquired such that locations of the three markers are identifiable in the three-dimensional image data, the markers being identifiable on the surface of the subject; and a transform calculating means for calculating a transform between positions of the markers on the subject denoted by selectively placing the wand pointer on each of the markers with the marker locations in the three-dimensional image data, whereby translational and rotational relationships between a subject space coordinate system and a three-dimensional image data space coordinate system. A system according to claim 6 wherein the markers contain materials which are visible in both magnetic resonance and CT imaging techniques such that the same markers can be used for both CT and magnetic resonance examinations. A system according to claim 1 wherein a plurality of reference emitters are mounted to the frame in fixed relationships to the receivers. A system according to claim 1 wherein the wand includes a tip portion, a portion extending along a pointing axis of the wand, and an offset portion which is offset from the pointing axis of the wand, the wand emitters being mounted in a spaced relationship to the offset section in alignment with the pointing axis of the wand such that the wand tip and the two actuators are co-linear. A system according to any one of the preceding claims which is a stereotaxy system. A position determining method comprising: a) securing a portion of a subject to a subject supporting surface in close proximity to at least three signal receivers that are mounted in a fixed relationship to the subject supporting surface; b) positioning a wand to designate selected locations on the subject portion, the wand having at least two wand emitters mounted thereon for selectively emitting signals which are received by the receivers; c) actuating the wand emitters to emit wand signals; d) from the wand emitter signals, calculating coordinates of the wand emitters in a coordinate system of the subject support; e) comparing a calculated distance between calculated wand emitter coordinates and a physical distance between the wand emitters; f) in response to the difference between the calculated distance and the physical distance exceeding a preselected standard, providing an unacceptable measurement signal. A position determining method comprising: a) securing a portion of a subject to a subject supporting surface in close proximity to at least three signal receivers that are mounted in a fixed relationship to the subject supporting surface, a reference signal emitter being fixedly mounted at a fixed, known distance from the plurality of receivers; b) positioning a wand to designate selected locations on the subject portion, the wand having at least two wand emitters mounted thereon for selectively emitting signals which are received by the receivers; c) actuating the wand emitters individually and the reference emitter in close temporal proximity to emit wand and reference signals; d) measuring travel durations for the wand and reference signals to travel from each of the wand emitters to the receivers and from the reference emitter to the receivers; e) from the travel times, calculating coordinates of the locations designated by the wand in a coordinate system of the subject support. A method according to claim 12 further including: calculating a distance between the wand emitters; comparing the calculated distance between the wand emitters with a premeasured physical distance between the emitters to verify an acceptable accuracy of the measurement. A method according to claim 13 further including sterilizing the wand. A method according to claim 13 further including repeating steps (b)-(e) with the wand in a second location to calculate coordinates of the second location and further including from the coordinates of the first and second locations, determining a distance therebetween. A method according to claim 13 wherein the subject support coordinates system coordinates calculating step includes: determining travel times between the wand emitters and the plurality of receivers, the relative travel times between each emitter and the receivers being indicative of a location of each emitter; correcting at least one of (i) the relative travel times between the wand emitters and the receivers and (ii) the determined positions of the emitters in accordance with the travel time between the reference emitter and at least one of the receivers, whereby the position of the wand is corrected for variations in signal transmission speed attributable to changes in temperature, humidity, and other conditions adjacent the subject. A method according to claim 16 wherein: the two wand emitters are actuated alternately a plurality of times; the reference emitter is actuated at least once; the travel times are adjusted for delays between (i) actuation of the emitter and emission of the signal and between (ii) the signal reaching the receiver and being converted into an electronic timing signal; the correcting step includes correcting the travel times between the wand emitters and the receivers in accordance with the travel time between the reference emitter and the receivers; and further including: averaging the corrected travel times and determining coordinates for each wand emitter; from the wand emitter coordinates calculating a coordinate of a tip portion of the wand. A method according to claim 13 further including: conducting a first non-invasive diagnostic examination of the subject portion and generating three-dimensional electronic image data thereof; storing the three-dimensional image data; determining a transform between the first image data coordinate system and the subject support coordinate system. A method according to claim 18 further including: conducting a second non-invasive diagnostic examination of the subject portion and generating three-dimensional electronic image data thereof; storing the second examination three-dimensional image data; determining a transform between the second image data coordinate system and the subject support coordinate system; determining a relationship between the first and second image data coordinate systems. A method according to claim 18 wherein the transform determining step includes: mounting at least three non-invasive examination visible markers to the subject portion such that the three-dimensional diagnostic image data includes indications of the at least three markers; with the wand designating a position of each of the three markers and determining a coordinate of each marker in the subject support coordinate system; comparing the coordinates of the markers in the subject support coordinate system and a position of the marker indications in the image data coordinate system to determine at least a translation offset between the image data and subject support coordinate systems and a rotational offset between the subject support and image data coordinate systems. A method according to claim 18 wherein the subject is a living patient. A method according to claim 12 wherein the subject portion is a head of the patient. A method according to any one of claims 11 to 22 which is a stereotaxy method.

Inventors: BARNETT GENE H, KORMOS DONALD W, STEINER CHARLES P, BARNETT, GENE H., KORMOS, DONALD W., STEINER, CHARLES P:
Applicants: CLEVELAND CLINIC FOUNDATION, THE CLEVELAND CLINIC FOUNDATION
Application year: 1993
Main classification: A61B19
IPC codes: G01B11, A61B10, A61B19, A61B17