Patent Application
20190223689
The invention relates generally to a medical device and particularly to an apparatus and methods associated with a range of image guided medical procedures.
Image guided surgery (IGS), also known as image guided intervention (IGI), enhances a physician's ability to locate instruments within anatomy during a medical procedure. IGS can include 2-dimensional (2-D), 3-dimensional (3-D), and 4-dimensional (4-D) applications. The fourth dimension of IGS can include multiple parameters either individually or together such as time, motion, electrical signals, pressure, airflow, blood flow, respiration, heart beat, and other patient measured parameters.
Existing imaging modalities can capture the movement of dynamic anatomy. Such modalities include electrocardiogram (ECG)-gated or respiratory-gated magnetic resonance imaging (MRI) devices, ECG-gated or respiratory-gated computer tomography (CT) devices, standard computed tomography (CT), 3D Fluoroscopic images (Angio-suites), and cinematography (CINE) fluoroscopy and ultrasound. Multiple image datasets can be acquired at different times, cycles of patient signals, or physical states of the patient. The dynamic imaging modalities can capture the movement of anatomy over a periodic cycle of that movement by sampling the anatomy at several instants during its characteristic movement and then creating a set of image frames or volumes.
A need exists for an apparatus that can be used with such imaging devices to capture pre-procedural or intra-procedural images of a targeted anatomical body and use those images intra-procedurally to help guide a physician to the correct location of the anatomical body during a medical procedure.
A method includes receiving during a first time interval image data associated with an image of a dynamic body. The image data includes an indication of a position of a first marker on a patient tracking device (PTD) coupled to the dynamic body and a position of a second marker on the PTD. Some registration methods such as 2D to 3D registration techniques allow for the image data containing the target or patient anatomy of interest to not contain the PTD. A registration step is performed to calculate the transformation from image space to patient space using an additional dataset to register (i.e., a 2D fluoroscopic set of images is used to register a 3D fluoroscopic dataset). This technique is not limited to fluoroscopic procedures as it can implemented in any procedure acquiring 2D images such as ultrasound, OCT (optical coherence tomography), EBUS (endobronchial ultrasound), or IVUS (intravascular ultrasound). This technique uses the markers that are within multiple 2D images to register the 3D volume that is reconstructed from these 2D images. The reconstructed 3D volume is smaller than the field of view of the 2D images, so this technique allows for the PTD markers to be visible in a subset of the 2D images, but not within the 3D volume. In certain embodiments, the first marker is coupled to the PTD at a first location and the second marker is coupled to the PTD at a second location. A distance between the position of the first marker and the position of the second marker is determined. During a second time interval after the first time interval, data associated with a position of a first localization element coupled to the PTD at the first location and data associated with a position of a second localization element coupled to the PTD at the second location are received. A distance between the first localization element and the second localization element based on the data associated with the position of the first localization element and the position of the second localization element is determined. A difference is calculated between the distance between the first marker and the second marker during the first time interval and the distance between the first localization element and the second localization element during the second time interval. In addition the PTD device can be tracked continuously during the procedure and a sequence of motion of the PTD device that represents the patient motion of an organ or the patient's respiratory cycle can be collected. The sequence of motion can then be analyzed to find unique similar points within the dataset and grouped.
Other objects and features will be in part apparent and in part pointed out hereinafter.
The details of the present invention, both as to its construction and operation can best be understood with reference to the accompanying drawings, in which like numerals refer to like parts, and in which:
The accompanying Figures and this description depict and describe embodiments of a navigation system (and related methods and devices) in accordance with the present invention, and features and components thereof. It should also be noted that any references herein to front and back, right and left, top and bottom and upper and lower are intended for convenience of description, not to limit the present invention or its components to any one positional or spatial orientation.
It is noted that the terms “comprise” (and any form of comprise, such as “comprises” and “comprising”), “have” (and any form of have, such as “has” and “having”), “contain” (and any form of contain, such as “contains” and “containing”), and “include” (and any form of include, such as “includes” and “including”) are open-ended linking verbs. Thus, a method, an apparatus, or a system that “comprises,” “has,” “contains,” or “includes” one or more items possesses at least those one or more items, but is not limited to possessing only those one or more items. For example, a method that comprises receiving a position of an instrument reference marker coupled to an instrument; transforming the position into image space using a position of a non-tissue internal reference marker implanted in a patient; and superimposing a representation of the instrument on an image in which the non-tissue internal reference marker appears possesses at least the receiving, transforming, and superimposing steps, but is not limited to possessing only those steps. Accordingly, the method also covers instances where the transforming includes transforming the position into image space using a transformation that is based, in part, on the position of the non-tissue internal reference marker implanted in the patient, and calculating the transformation using image space coordinates of the internal reference marker in the image. The term “use” should be interpreted the same way. Thus, a calculation that uses certain items uses at least those items, but also covers the use of additional items.
Individual elements or steps of the present methods, apparatuses, and systems are to be treated in the same manner. Thus, a step that calls for creating a dataset that includes images, one of the images (a) depicting a non-tissue internal reference marker, (b) being linked to non-tissue internal reference marker positional information, and (c) being at least 2-dimensional covers the creation of at least such a dataset, but also covers the creation of a dataset that includes images, where each image (a) depicts the non-tissue internal reference marker, and (b) is linked to non-tissue internal reference marker positional information.
The terms “a” and “an” are defined as one or more than one. The term “another” is defined as at least a second or more. The term “coupled” encompasses both direct and indirect connections, and is not limited to mechanical connections.
Those of skill in the art will appreciate that in the detailed description below, certain well known components and assembly techniques have been omitted so that the present methods, apparatuses, and systems are not obscured in unnecessary detail.
An apparatus according to an embodiment of the invention includes a PTD and two or more markers coupled to the PTD. The apparatus can also include two or more localization elements coupled to the PTD proximate the markers. The apparatus is configured to be coupled to a dynamic body, such as selected dynamic anatomy of a patient. Dynamic anatomy can be, for example, any anatomy that moves during its normal function (e.g., the heart, lungs, kidneys, liver and blood vessels). A processor, such as a computer, is configured to receive image data associated with the dynamic body taken during a pre-surgical or pre-procedural first time interval. The image data can include an indication of a position of each of the markers for multiple instants in time during the first time interval. The processor can also receive position data associated with the localization elements during a second time interval in which a surgical procedure or other medical procedure is being performed. The processor can use the position data received from the localization elements to determine a distance between the elements for a given instant in time during the second time interval. The processor can also use the image data to determine the distance between the markers for a given instant in time during the first time interval. The processor can then find a match between an image where the distance between the markers at a given instant in time during the first time interval is the same as the distance between the elements associated with those markers at a given instant in time during the medical procedure, or second time interval. Additionally the processor can determine a sequence of motion of the markers and match this sequence of motion to the recorded motion of the markers over the complete procedure or significant period of time. Distance alone between the markers may not be sufficient to match the patient space to image space in many instances, it is important for the system to know the direction the markers are moving and the range and speed of this motion to find the appropriate sequence of motion for a complex signal or sequence of motion by the patient.
A physician or other healthcare professional can use the images selected by the processor during a medical procedure performed during the second time interval. For example, when a medical procedure is performed on a targeted anatomy of a patient, such as a heart or lung, the physician may not be able to utilize an imaging device during the medical procedure to guide him to the targeted area within the patient. A PTD according to an embodiment of the invention can be positioned or coupled to the patient proximate the targeted anatomy prior to the medical procedure, and pre-procedural images can be taken of the targeted area during a first time interval. Markers or fiducials coupled to the PTD can be viewed with the image data, which can include an indication of the position of the markers during a given path of motion of the targeted anatomy (e.g., the heart) during the first time interval. Such motion can be due, for example, to inspiration (i.e., inhaling) and expiration (i.e., exhaling) of the patient, or due to the heart beating. During a medical procedure, performed during a second time interval, such as a procedure on a heart or lung, the processor receives data from the localization elements associated with a position of the elements at a given instant in time during the medical procedure (or second time interval). The distance between selected pairs of markers can be determined from the image data and the distance, range, acceleration, and speed between corresponding selected pairs of localization elements can be determined based on the element data for given instants in time. From multiple image datasets the range and speed of the markers motion can be calculated.
Because the localization elements are coupled to the PTD proximate the location of the markers, the distance between a selected pair of elements can be used to determine an intra-procedural distance between the pair of corresponding markers to which the localization elements are coupled. An image from the pre-procedural image data taken during the first time interval can then be selected where the distance between the pair of selected markers in that image corresponds with or closely approximates the same distance determined using the localization elements at a given instant in time during the second time interval. This process can be done continuously during the medical procedure, producing simulated real-time, intra-procedural images illustrating the orientation and shape of the targeted anatomy as a catheter, sheath, needle, forceps, guidewire, fiducial delivery devices, therapy device (ablation modeling, drug diffusion modeling, etc.) or similar structure(s) is/are navigated to the targeted anatomy. Thus, during the medical procedure, the physician can view selected image(s) of the targeted anatomy that correspond to and simulate real-time movement of the anatomy. In addition, during a medical procedure being performed during the second time interval, such as navigating a catheter or other instrument or component thereof to a targeted anatomy, the location(s) of a sensor (e.g., an electromagnetic coil sensor) coupled to the catheter during the second time interval can be superimposed on an image of a catheter. The superimposed image(s) of the catheter can then be superimposed on the selected image(s) from the first time interval, providing simulated real-time images of the catheter location relative to the targeted anatomy. This process and other related methods are described in pending U.S. patent application Ser. No. 10/273,598, entitled Methods, Apparatuses, and Systems Useful in Conducting Image Guided Interventions, filed Nov. 8, 2003, the entire disclosure of which is incorporated herein by reference.
As discussed herein, auto registration of a device is conducted, at least initially, by finding the PTD. In general, the PTD needs to be within the 3D volume, but for some devices the 3D volume may be too small to include both the PTD and the target. To overcome this, a 2D/3D algorithm can be employed in accordance with various embodiments, whereby multiple 2D images of a patient are acquired for a 3D volume reconstruction. The complete PTD (which may include one, two or multiple (e.g., at least 3) sensors or fiducials) does not need to be seen in each image; e.g., some images may only show one sensor or a part thereof, but the entire collection of 2D images can be compiled and used to find the whole or entire PTD relative to the target. For example, 180 2D images (or more or less depending on patient/device position, etc.) can be used to construct a complete 3D volume (where only a fraction (e.g., 10-30) of the 2D images include all or a portion of the PTD. This facilitates easier device placement and allows the user to focus on the target, as the PTD and target do not necessarily need to be in the same initial 3D volume.
In one embodiment, a real-time pathway registration is applied to a pre-acquired dataset that does not contain the PTD. It will be understood that the pre-acquired dataset can be at only one cycle of a patient's respiratory, heartbeat, or other path of motion. In order to optimize the registration of a pre-acquired dataset that does not contain the PTD, a PTD can be subsequently applied to the patient, and the PTD signal can be used to collect registration information throughout full range or path of motion but only that information that is captured at a similar PTD orientation, shape, or point along the PTD cycle of motion is used. This method enhances the registration accuracy by ensuring that the registration points being used to register are at the same point during the initial dataset acquisition. In preferred embodiments, the method uses multiple subsets of the acquired registration data that are collected based on the PTD signal. These multiple subsets are then applied against the pre-acquired dataset to find the optimal registration fit.
One aspect is directed to recording 3D location and bronchoscopic video to construct a 3D model of the patient's airway. This 3D video can be recorded over multiple sessions (e.g., weeks between recording) and color, size, and shape analysis/change can be determined and/or compared for diagnostic purposes. Not only can airway lumen size and/or shape be compared, but a deformation or vector field can also be compared for the multiple sessions. This can be particularly valuable in determining overall lung function change as well as local changes to muscle and tissue elasticity.
Another similar aspect is directed to recording 3D location and EBUS video or images to construct a 3D model of the patient's airway or a lesion. Typically, the EBUS image is very small and 2D. Thus, recording multiple planes of EBUS can be used to create a 3D image of the lesion, lymph node, or blood vessels. Providing correlated CT information to the EBUS image can be valuable in determining the location of structures in the patient.
Yet another similar aspect is directed to recording 3D location and IVUS video or images to construct a 3D model of the patient's blood vessels or plaques. Like EBUS, the IVUS image is typically very small and 2D. Recording multiple planes of IVUS can be used to create a 3D image of the blood vessels and malformations. Providing correlated CT information to the IVUS image can be valuable in determining the location of structures in the patient. In accordance with this and other aspects, OCT may additionally or alternatively employed.
In another embodiment, the device can be integrated with one or more fiber optic localization (FDL) devices and/or techniques. In this way, the sensor (such as an EM sensor) provides the 3D spatial orientation of the device, while the FDL provides shape sensing of the airway, vessel, pathway, organ, environment and surroundings. Conventional FDL techniques can be employed. In various embodiments, for example, the FDL device can be used to create localization information for the complete pathway or to refine the localization accuracy in a particular segment of the pathway. By either using 3D localization information, shape, or both detected by the FDL device, the system can use a weighted algorithm between multiple localization devices to determine the location and orientation of the instrument in the patient. The FDL device can also be used as or in conjunction with the PTD to track the patient's motion such as respiration or heartbeat.
In another aspect, a high-speed three-dimensional imaging device, such as an optical coherence tomography (OCT) device, can be tracked. In accordance with conventional methods, such a device can only view 1-2 mm below the surface. With an EM sensor attached in accordance with the systems and methods described herein, multiple 3D volumes of data can be collected and a larger 3D volume of collected data can be constructed. Knowing the 3D location and orientation of the multiple 3D volumes will allow the user to view a more robust image of, for example, pre-cancerous changes in the esophagus or colon. This data can also be correlated to pre-acquired or intra-procedurally acquired CT, fluoroscopic, ultrasound, or 3D fluoroscopic images to provide additional information.
In general, the methods described herein involve increasing registration accuracy for Ultrasound (US) to CT or any other 3D image dataset such as MR, CT-PET, and 3D Ultrasound. Using 4D tracking of the patient respiratory signal and collecting a cine loop of ultrasound images, one can maximize the US to CT fusion accuracy by limiting the point or plane selection for registration to the correct respiratory cycle that matches the 3D dataset. The process involves the use of a patient tracker on the patient and a tracker on the US transducer; using a localizer (such as an EM localization system) to record a cine loop of US images and match the images in the cine loop to the respiratory signal.
Collecting a cine loop of US data for registration is valuable in that the user does not necessarily have to select a moving point while the patient is breathing. The user can simply scroll through the cine loop and, with an indicator of the point in the respiratory cycle, select the points that are best used for registration from a static image.
The user then selects, for example, at least 3 points in the US & CT datasets, or a plane and at least one point to register the US space to the 3D CT dataset space. Preferably, the points and plane are selected at the same respiratory point as the 3D CT dataset. Normally, for example, the 3D CT dataset would be acquired at exhalation. Therefore, the user preferably selects registration points at exhalation or significant errors can be incorporated into the US to CT registration. If a user was to select a plane that was at a different point in the respiratory cycle, for instance, there would be significant translation error in the registration. There would likely also be significant rotational error in the registration if the points were acquired at different points in the respiratory cycle.
The methods and systems described herein can be expanded to use other patient sensing information such as cardiac information (heartbeat) as a single source 4D signal or multiple sensed signal approach in that respiration and cardiac data could be used together. This is particularly relevant in connection with locations close to the heart or within the heart.
Preferably, the user selects points that are sufficiently far apart for the best accuracy. This can be done, for example, by requiring the user to record a cine loop of data that extends over the whole patient organ. Preferably, the user is not allowed to pick multiple points in the same image.
Another technique for maximizing registration accuracy is a centroid finding algorithm that can be used for refining point locations in a local area. Often, a user will want to select a vessel bifurcation. The vessel bifurcation will be seen as a bright white location on the CT and US images. An algorithm can be used to help the user select the optimal center location for these locations. Once a user selects a point on the image, the local algorithm can be employed to find similar white voxels that are connected and, for that shape in the 3D space, refine the point to the centroid or any other optimal point (such as, for example, the most anterior or most posterior point).
In general, the systems and methods described herein can be implemented regardless of the number of sensors that are used. In some embodiments, serial orientation or positioning of multiple sensors allows the determination of one or more parameters such as shape, position, orientation, and mechanical status of a complete or partial section of guidewire or other device or instrument. For example, the placement of multiple sensors can assist in visualizing the shape of the device and any bends in the path by providing a number of data points on the path (e.g., 8 sensors, spaced 1 mm apart) to create a 3D shape model of the device. Various parameters can be used to track past or present movement and changes in device shape including, for example, elasticity, bend radius, limiting, and durometer rating of the device material. These parameters and accompanying data can provide visual cues to the user during the procedure, for example, when the device has a certain bend or curvature (based on path or surroundings), e.g., to provide a notice or warning that the device is on the correct or incorrect path, or to provide notice regarding, or track, a particular parameter(s) that the user is interested in. Such a sensor pathway is generally depicted in
In various aspects and embodiments described herein, one can use the knowledge of the path traveled by the instrument and segmented airway or vessel from the acquired image (e.g., CT) to limit the possibilities of where the instrument is located in the patient. The techniques described herein, therefore, can be valuable to improve virtual displays for users. Fly through, Fly-above, or image displays related to segmented paths are commonly dependent upon relative closeness to the segmented path. For a breathing patient, for example, or a patient with a moving vessel related to heartbeat, it is valuable to use the path traveled information to determine where in the 4D patient motion cycle the system is located within the patient. By comparing the 3D location, the patient's tracked or physiological signal is used to determine 4D patient motion cycle, and with the instrument's traveled path, one can determine the optical location relative to a segmented airway or vessel and use this information to provide the optimal virtual display.
Two or more markers or fiducials 22 are coupled to the PTD 20 at selected locations as shown in
An imaging device 40 can be used to take images of the dynamic body B while the PTD 20 is coupled to the dynamic body B, pre-procedurally during a first time interval. As stated above, the markers 22 are visible on the images and can provide an indication of a position of each of the markers 22 during the first time interval. The position of the markers 22 at given instants in time through a path of motion of the dynamic body B can be illustrated with the images. The imaging device 40 can be, for example, a computed tomography (CT) device (e.g., respiratory-gated CT device, ECG-gated CT device), a magnetic resonance imaging (MRI) device (e.g., respiratory-gated MRI device, ECG-gated MRI device), an X-ray device, or any other suitable medical imaging device. In one embodiment, the imaging device 40 is a computed tomography-positron emission tomography device that produces a fused computed tomography-positron emission tomography image dataset. The imaging device 40 can be in communication with a processor 30 and send, transfer, copy and/or provide image data taken during the first time interval associated with the dynamic body B to the processor 30.
The processor 30 includes a processor-readable medium storing code representing instructions to cause the processor 30 to perform a process. The processor 30 can be, for example, a commercially available personal computer, or a less complex computing or processing device that is dedicated to performing one or more specific tasks. For example, the processor 30 can be a terminal dedicated to providing an interactive graphical user interface (GUI). The processor 30, according to one or more embodiments of the invention, can be a commercially available microprocessor. Alternatively, the processor 30 can be an application-specific integrated circuit (ASIC) or a combination of ASICs, which are designed to achieve one or more specific functions, or enable one or more specific devices or applications. In yet another embodiment, the processor 30 can be an analog or digital circuit, or a combination of multiple circuits.
The processor 30 can include a memory component 32. The memory component 32 can include one or more types of memory. For example, the memory component 32 can include a read only memory (ROM) component and a random access memory (RAM) component. The memory component can also include other types of memory that are suitable for storing data in a form retrievable by the processor 30. For example, electronically programmable read only memory (EPROM), erasable electronically programmable read only memory (EEPROM), flash memory, as well as other suitable forms of memory can be included within the memory component. The processor 30 can also include a variety of other components, such as for example, coprocessors, graphic processors, etc., depending upon the desired functionality of the code.
The processor 30 can store data in the memory component 32 or retrieve data previously stored in the memory component 32. The components of the processor 30 can communicate with devices external to the processor 30 by way of an input/output (I/O) component (not shown). According to one or more embodiments of the invention, the I/O component can include a variety of suitable communication interfaces. For example, the I/O component can include, for example, wired connections, such as standard serial ports, parallel ports, universal serial bus (USB) ports, S-video ports, local area network (LAN) ports, small computer system interface (SCCI) ports, and so forth. Additionally, the I/O component can include, for example, wireless connections, such as infrared ports, optical ports, Bluetooth® wireless ports, wireless LAN ports, or the like.
The processor 30 can be connected to a network, which may be any form of interconnecting network including an intranet, such as a local or wide area network, or an extranet, such as the World Wide Web or the Internet. The network can be physically implemented on a wireless or wired network, on leased or dedicated lines, including a virtual private network (VPN).
As stated above, the processor 30 can receive image data from the imaging device 40. The processor 30 can identify the position of selected markers 22 within the image data or voxel space using various segmentation techniques, such as Hounsfield unit thresholding, convolution, connected component, or other combinatory image processing and segmentation techniques. The processor 30 can determine a distance and direction between the position of any two markers 22 during multiple instants in time during the first time interval, and store the image data, as well as the position and distance data, within the memory component 32. Multiple images can be produced providing a visual image at multiple instants in time through the path of motion of the dynamic body. The processor 30 can also include a receiving device or localization device 34, which is described in more detail below.
A deformation field may also be included in the analysis in various embodiments described herein. For example, the deformation field can be applied to fuse 3D fluoroscopic images to CT images in order to compensate for different patient orientations, patient position, respiration, deformation induced by the catheter or other instrument, and/or other changes or perturbations that occur due to therapy delivery or resection or ablation of tissue.
In some embodiments, for example, real-time respiration compensation can be determined by applying an inspiration-to-expiration deformation vector field. In combination with the PTD respiratory signal, for example, the instrument location can be calculated using the deformation vector field. A real-time instrument tip correction vector can be applied to a 3D localized instrument tip. The real-time correction vector is computed by scaling an inspiration-to-expiration deformation vector (found from the inspiration-to-expiration deformation vector field) based on the PTD respiratory signal. This correction vector can then be applied to the 3D localized instrument tip. This can further optimize accuracy during navigation.
An example of an algorithm for real-time respiration compensation can be found in :
(a) find vi such that scalar d is minimized;
(b) compute c, wherein:
c=−v
i
t
and (c) compute ′, wherein:
′=
+c
Thus, ′ is a respiration compensated version of
.
Although
Deformation on 2D images can also be calculated based upon therapeutic change of tissue, changes in Houndsfield units for images, patient motion compensation during the imaging sequence, therapy monitoring, and temperature monitoring with fluoroscopic imaging, among other things. One potential issue with conventional therapy delivery, for instance, is monitoring the therapy for temperature or tissue changes. In accordance with the methods described herein, this monitoring can be carried out using intermittent fluoroscopic imaging, where the images are compensated between acquisition times to show very small changes in image density, which can represent temperature changes or tissue changes as a result of the therapy and/or navigation.
In general, it may also be preferable to reduce the level of radiation that patients are exposed to before or during a procedure (or pre-procedural analysis) as described herein. One method of reducing radiation during the acquisition of a 3D fluoroscopic dataset (or other dataset described herein), for example, is to use a deformation field between acquired 2D images to reduce the actual number of 2D images that need to be acquired to create the 3D dataset. In one particular embodiment, the deformation field is used to calculate the deformation between images in the acquisition sequence to produce 2D images between the acquired slices, and these new slices can be used to calculate the 3D fluoroscopic dataset. For example, if 180 2D image slices were previously required, e.g., an image(s) taken every 2 degrees of a 360 degree acquisition sequence, in accordance with some embodiments 90 2D images can be acquired over a 360 degree acquisition sequence and the data from the images that would have ordinarily been acquired between each slice can be calculated and imported into the 3D reconstruction algorithm. Thus, the radiation is effectively reduced by 50%.
As shown in
An image can then be selected from the pre-operative images taken during the first time interval that indicates a distance or is grouped in a similar sequence of motion between corresponding markers 22 at a given instant in time, that most closely approximates or matches the distance or similar sequence of motion between the selected elements 24. The process of comparing the distances is described in more detail below. Thus, the apparatus 10 and processor 30 can be used to provide images corresponding to the actual movement of the targeted anatomy during the medical procedure being performed during the second time interval. The images illustrate the orientation and shape of the targeted anatomy during a path of motion of the anatomy, for example, during inhaling and exhaling.
One method of selecting the appropriate image from the pre-procedural images is to execute an algorithm that can sum all of the distances a1 through a6 and then search for and match this sum to an image containing a sum of all of the distances d1 through d6 obtained pre-procedurally from the image data that is equal to the sum of the distances a1 through a6. When the difference between these sums is equal to zero, the relative position and orientation of the anatomy or dynamic body D during the medical procedure will substantially match the position and orientation of the anatomy in the particular image. The image associated with distances d1 through d6 that match or closely approximate the distances a1 through a6 can then be selected and displayed. For example,
Does Σai=Σdi(i=1 to 6 in this example) OR
Does Σ(ai−di)=0(i=1 to 6 in this example).
If yes to either of these, then the image is a match to the vector or distance data obtained during the medical procedure.
Then at step 60, during a second time interval, while performing a medical procedure on the patient with the PTD positioned on the patient at substantially the same location, position data can be received for a first localization element and a second localization element. The localization elements can be coupled to the PTD proximate the locations of the markers, such that the position data associated with the elements can be used to determine the relative position of the markers in real-time during the medical procedure. The position data of the elements can be stored and/or recorded at step 62.
A distance between the first and second localization elements can be determined at step 64. Although only two localization elements are described, as with the markers, position data associated with more than two localization elements can be received and the distances between the additional elements can be determined.
The next step is to determine which image from the one or more images taken during the first time interval represents the relative position and/or orientation of the dynamic body at a given instant in time during the second time interval or during the medical procedure. To determine this, at step 66, the distance between the positions of the first and second localization elements at a given instant in time during the second time interval are compared to the distance(s) determined in step 56 between the positions of the first and second markers obtained with the image data during the first time interval.
An image can be selected from the first time interval that best represents the same position and orientation of the dynamic body at a given instant in time during the medical procedure. To do this, the difference between the distance between a given pair of localization elements during the second time interval is used to select the image that contains the same distance between the same given pair of markers from the image data received during the first time interval. This can be accomplished, for example, by executing an algorithm to perform the calculations. When there are multiple pairs of markers and localization elements, the algorithm can sum the distances between all of the selected pairs of elements for a given instant in time during the second time interval and sum the distances between all of the associated selected pairs of markers for each instant in time during the first time interval when the pre-procedural image data was received.
When an image is found that provides the sum of distances for the selected pairs of markers that is substantially the same as the sum of the distances between the localization elements during the second time interval, then that image is selected at step 68. The selected image can then be displayed at step 70. The physician can then observe the image during the medical procedure on a targeted portion of the dynamic body. Thus, during the medical procedure, the above process can be continuously executed such that multiple images are displayed and images corresponding to real-time positions of the dynamic body can be viewed.
Specifically,
As noted herein, a variety of instruments and devices can be used in conjunction with the systems and methods described herein. In one embodiment, for example, an angled coil sensor is employed during the targeted navigation. In accordance with this embodiment, for example, instead of using a conventional wire sensor wrapped at about a 90° angle (i.e., roughly perpendicular) to the axial length (or core) of the sensor, the coil is wrapped at an acute angle (i.e., the angle is less than about 90°) relative to the axial length of the sensor. In one embodiment, the coil is positioned (e.g., wrapped) at an angle of from about 30° to about 60° relative to the axial length. In one preferred embodiment, the coil is positioned at about a 45° angle relative to the axial length. The positioning of the coil in accordance with the exemplary embodiments described herein advantageously provides a directional vector that is not parallel with the sensor core. Thus, the physical axis is different and, as the sensor moves, this additional directional vector can be quantified and used to detect up and down (and other directional) movement. This motion can be captured over time as described herein to determine orientation and prepare and display the more accurate images.
An external reference marker 22 can be placed in a location close to the region of the patient where the procedure is to be performed, yet in a stable location that will not move (or that will move a negligible amount) with the patient's heart beat and respiration. If patient 10 is securely fixed to table 12 for the procedure, external reference marker 22 (which may be described as “static”) can be affixed to table 12. If patient 10 is not completely secured to table 12, external reference marker 22 can be placed on region of the back of patient 10 exhibiting the least amount of movement. Tracker 20 can be configured to track external reference marker 22.
One or more non-tissue internal reference markers 24 can be placed in the gross region where the image guided navigation will be carried out. Non-tissue internal reference marker(s) 24 should be placed in an anatomic location that exhibits movement that is correlated with the movement of the anatomy intended for image guided navigation. This location will be internal to the patient, in the gross location of the anatomy of interest.
Medical instrument 16, instrument reference marker(s) 18, external reference marker 22, and non-tissue internal reference marker(s) 24 can be coupled to converter 26 of system 100. Converter 26, one example of which may be referred to in the art as a break-out box, can be configured to convert analog measurements received from the reference markers and tracker 20 into digital data understandable by image guidance computing platform 30, and relay that data to image guidance computing platform 30 to which converter 26 can be coupled. Image guidance computing platform 30 can take the form of a computer, and may include a monitor on which a representation of one or more instruments used during the IGI can be displayed over an image of the anatomy of interest.
System 100 also includes a periodic human characteristic signal monitor, such as ECG monitor 32, which can be configured to receive a periodic human characteristic signal. For example, ECG monitor 32 can be configured to receive an ECG signal in the form of the ECG data transmitted to it by ECG leads 34 coupled to patient 10. The periodic human characteristic signal monitor (e.g., ECG monitor 32) can also be configured to relay a periodic human characteristic signal (e.g., ECG data) to image guidance computing platform 30, to which it can be coupled.
Prior to the start of the image guided intervention, non-tissue internal reference marker(s) 24—but not necessarily static external reference marker 22—should be placed in the gross region of interest for the procedure. After placement of non-tissue internal reference marker(s) 24, patient 10 is to be scanned with an imaging device, such as gated scanner 40, and the resulting gated image dataset transferred to image guidance computing platform 30, to which the imaging device is coupled and which can reside in the operating or procedure theatre. Examples of suitable imaging devices, and more specifically suitable gated scanners, include ECG-gated MRI scanners and ECG-gated CT scanners. A hospital network 50 may be used to couple gated scanner 40 to image guidance computing platform 30.
The imaging device (e.g., gated scanner 40) can be configured to create a gated dataset that includes pre-operative images, one or more of which (up to all) are taken using the imaging device and are linked to a sample of a periodic human characteristic signal (e.g., a sample, or a phase, of an ECG signal). Once patient 10 is scanned using the imaging device and the gated dataset is transferred to and received by image guidance computing platform 30, patient 10 can be secured to operating table 12 and the equipment making up system 100 (e.g., tracker 20, converter 26, image guidance computing platform 30, ECG monitor 32, and gated scanner 40) set up as shown in
At this point, a gated dataset created by gated scanner 40 resides on image guidance computing platform 30.
The surgical instrument 12 is preferably a relatively inexpensive, flexible and/or steerable catheter that may be of a disposable type. The surgical instrument 12 is modified to include one or more tracking sensors that are detectable by the tracking subsystem 20. It is readily understood that other types of surgical instruments (e.g., a guide wire, a needle, a forcep, a pointer probe, a stent, a seed, an implant, an endoscope, an energy delivery device, a therapy delivery device, etc.) are also within the scope of the present invention. It is also envisioned that at least some of these surgical instruments may be wireless or have wireless communications links. It is also envisioned that the surgical instruments may encompass medical devices which are used for exploratory purposes, testing purposes or other types of medical procedures.
The volumetric scan data is then registered as shown at 34. Registration of the dynamic reference frame 19 generally relates information in the volumetric scan data to the region of interest associated with the patient. This process is referred to as registering image space to patient space. Often, the image space must also be registered to another image space. Registration is accomplished through knowledge of the coordinate vectors of at least three non-collinear points in the image space and the patient space.
Referring to
The multi-dimensional imaging modalities described herein may also be coupled with digitally reconstructed radiography (DRR) techniques. In accordance with a fluoroscopic image acquisition, for example, radiation passes through a physical media to create a projection image on a radiation-sensitive film or an electronic image intensifier. Given a 3D or 4D dataset as described herein, for example, a simulated image can be generated in conjunction with DRR methodologies. DRR is generally known in the art, and is described, for example, by Lemieux et al. (Med. Phys. 21(11), November 1994, pp. 1749-60).
When a DRR image is created, a fluoroscopic image is formed by computationally projecting volume elements, or voxels, of the 3D or 4D dataset onto one or more selected image planes. Using a 3D or 4D dataset of a given patient as described herein, for example, it is possible to generate a DRR image that is similar in appearance to a corresponding patient image. This similarity can be due, at least in part, to similar intrinsic imaging parameters (e.g., projective transformations, distortion corrections, etc.) and extrinsic imaging parameters (e.g., orientation, view direction, etc.). The intrinsic imaging parameters can be derived, for instance, from the calibration of the equipment. Advantageously, this provides another method to see the up-and-down (and other directional) movement of the instrument. This arrangement further provides the ability to see how the device moves in an image(s), which translates to improved movement of the device in a patient. An exemplary pathway in accordance with the disclosure herein can be seen in
A dynamic reference frame 19 is attached to the patient proximate to the region of interest within the patient 13. To the extent that the region of interest is a vessel or a cavity within the patient, it is readily understood that the dynamic reference frame 19 may be placed within the patient 13. To determine its location, the dynamic reference frame 19 is also modified to include tracking sensors detectable by the tracking subsystem 20. The tracking subsystem 20 is operable to determine position data for the dynamic reference frame 19 as further described below.
The volumetric scan data is then registered as shown at 34. Registration of the dynamic reference frame 19 generally relates information in the volumetric scan data to the region of interest associated with the patient. This process is referred to as registering image space to patient space. Often, the image space must also be registered to another image space. Registration is accomplished through knowledge of the coordinate vectors of at least three non-collinear points in the image space and the patient space.
Registration for image guided surgery can be completed by different known techniques. First, point-to-point registration is accomplished by identifying points in an image space and then touching the same points in patient space. These points are generally anatomical landmarks that are easily identifiable on the patient. Second, surface registration involves the user's generation of a surface in patient space by either selecting multiple points or scanning, and then accepting the best fit to that surface in image space by iteratively calculating with the data processor until a surface match is identified. Third, repeat fixation devices entail the user repeatedly removing and replacing a device (i.e., dynamic reference frame, etc.) in known relation to the patient or image fiducials of the patient. Fourth, automatic registration by first attaching the dynamic reference frame to the patient prior to acquiring image data. It is envisioned that other known registration procedures are also within the scope of the present invention, such as that disclosed in U.S. Ser. No. 09/274,972, filed on Mar. 23, 1999, entitled “NAVIGATIONAL GUIDANCE VIA COMPUTER-ASSISTED FLUOROSCOPIC IMAGING”, which is hereby incorporated by reference herein.
Referring to
To eliminate the flutter of the indicia on the displayed image 40, position data for the surgical instrument 12 is acquired at a repetitive point within each cycle of either the cardiac cycle or the respiratory cycle of the patient. As described above, the imaging device 14 is used to capture volumetric scan data 42 representative of an internal region of interest within a given patient. A secondary image may then be rendered 44 from the volumetric scan data by the data processor 16.
In order to synchronize the acquisition of position data for the surgical instrument 12, the surgical instrument navigation system 10 may further include a timing signal generator 26. The timing signal generator 26 is operable to generate and transmit a timing signal 46 that correlates to at least one of (or both) the cardiac cycle or the respiratory cycle of the patient 13. For a patient having a consistent rhythmic cycle, the timing signal might be in the form of a periodic clock signal. Alternatively, the timing signal may be derived from an electrocardiogram signal from the patient 13. One skilled in the art will readily recognize other techniques for deriving a timing signal that correlate to at least one of the cardiac or respiratory cycle or other anatomical cycle of the patient.
As described above, the indicia of the surgical instrument 12 tracks the movement of the surgical instrument 12 as it is moved by the surgeon within the patient 13. Rather than display the indicia of the surgical instrument 12 on a real-time basis, the display of the indicia of the surgical instrument 12 is periodically updated 48 based on the timing signal from the timing signal generator 26. In one exemplary embodiment, the timing generator 26 is electrically connected to the tracking subsystem 20. The tracking subsystem 20 is in turn operable to report position data for the surgical instrument 12 in response to a timing signal received from the timing signal generator 26. The position of the indicia of the surgical instrument 12 is then updated 50 on the display of the image data. It is readily understood that other techniques for synchronizing the display of an indicia of the surgical instrument 12 based on the timing signal are within the scope of the present invention, thereby eliminating any flutter or jitter which may appear on the displayed image 52. It is also envisioned that a path (or projected path) of the surgical instrument 12 may also be illustrated on the displayed image data 52.
In another aspect of the present invention, the surgical instrument navigation system 10 may be further adapted to display four-dimensional image data for a region of interest as shown in
In order to synchronize the display of the volumetric perspective view in real-time with the cardiac or respiratory cycle of the patient, the data processor 16 is adapted to receive a timing signal from the timing signal generator 26. As described above, the timing signal generator 26 is operable to generate and transmit a timing signal that correlates to either the cardiac cycle or the respiratory cycle of the patient 13. In this way, the volumetric perspective image may be synchronized 66 with the cardiac or respiratory cycle of the patient 13. The synchronized image 66 is then displayed 68 on the display 18 of the system. The four-dimensional synchronized image may be either (or both of) the primary image rendered from the point of view of the surgical instrument or the secondary image depicting the indicia of the position of the surgical instrument 12 within the patient 13. It is readily understood that the synchronization process is also applicable to two-dimensional image data acquire over time.
To enhance visualization and refine accuracy of the displayed image data, the surgical navigation system can use prior knowledge such as the segmented vessel or airway structure to compensate for error in the tracking subsystem or for inaccuracies caused by an anatomical shift occurring since acquisition of scan data. For instance, it is known that the surgical instrument 12 being localized is located within a given vessel or airway and, therefore should be displayed within the vessel or airway. Statistical methods can be used to determine the most likely location; within the vessel or airway with respect to the reported location and then compensate so the display accurately represents the instrument 12 within the center of the vessel or airway. The center of the vessel or airway can be found by segmenting the vessels or airways from the three-dimensional datasets and using commonly known imaging techniques to define the centerline of the vessel or airway tree. Statistical methods may also be used to determine if the surgical instrument 12 has potentially punctured the vessel or airway. This can be done by determining the reported location is too far from the centerline or the trajectory of the path traveled is greater than a certain angle (worse case 90 degrees) with respect to the vessel or airway. Reporting this type of trajectory (error) is very important to the clinicians. The tracking along the center of the vessel may also be further refined by correcting for motion of the respiratory or cardiac cycle, as described above. While navigating along the vessel or airway tree prior knowledge about the last known location can be used to aid in determining the new location. The instrument or navigated device must follow a pre-defined vessel or airway tree and therefore can not jump from one branch to the other without traveling along a path that would be allowed. The orientation of the instrument or navigated device can also be used to select the most likely pathway that is being traversed. The orientation information can be used to increase the probability or weight for selected location or to exclude potential pathways and therefore enhance system accuracy.
The surgical instrument navigation system of the present invention may also incorporate atlas maps. It is envisioned that three-dimensional or four-dimensional atlas maps may be registered with patient specific scan data or generic anatomical models. Atlas maps may contain kinematic information (e.g., heart and lung models) that can be synchronized with four-dimensional image data, thereby supplementing the real-time information. In addition, the kinematic information may be combined with localization information from several instruments to provide a complete four-dimensional model of organ motion. The atlas maps may also be used to localize bones or soft tissue which can assist in determining placement and location of implants.
While various embodiments of the invention have been described above, it should be understood that they have been presented by way of example only, and not limitation. Thus, the breadth and scope of the invention should not be limited by any of the above-described embodiments, but should be defined only in accordance with the following claims and their equivalents.
The previous description of the embodiments is provided to enable any person skilled in the art to make or use the invention. While the invention has been particularly shown and described with reference to embodiments thereof, it will be understood by those skilled in art that various changes in form and details may be made therein without departing from the spirit and scope of the invention. For example, the PTD, markers and localization elements can be constructed from any suitable material, and can be a variety of different shapes and sizes, not necessarily specifically illustrated, while still remaining within the scope of the invention.
This application claims the benefit of U.S. Provisional Application Ser. No. 61/375,439, filed Aug. 20, 2010, 61/375,484, filed Aug. 20, 2010, 61/375,523, filed Aug. 20, 2010, and 61/375,533, filed Aug. 20, 2010, each of which are hereby incorporated by reference in their entirety, including any figures, tables, and drawings.
| Number | Date | Country | |
|---|---|---|---|
| 61375523 | Aug 2010 | US | |
| 61375533 | Aug 2010 | US | |
| 61375439 | Aug 2010 | US | |
| 61375484 | Aug 2010 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 14989692 | Jan 2016 | US |
| Child | 16371576 | US | |
| Parent | 13215050 | Aug 2011 | US |
| Child | 14989692 | US |
