METHODS AND APPARATUS FOR PATIENT POSITIONING IN MAGNETIC RESONANCE IMAGING
According to some aspects, a magnetic resonance imaging system capable of imaging a patient is provided. The magnetic resonance imaging system comprising at least one B0 magnet to produce a magnetic field to contribute to a B0 magnetic field for the magnetic resonance imaging system and a member configured to engage with a releasable securing mechanism of a radio frequency coil apparatus, the member attached to the magnetic resonance imaging system at a location so that, when the member is engaged with the releasable securing mechanism of the radio frequency coil apparatus, the radio frequency coil apparatus is secured to the magnetic resonance imaging system substantially within an imaging region of the magnetic resonance imaging system.
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This application claims priority under 35 U.S.C. § 120 and is a continuation (CON) of U.S. patent application Ser. No. 16/516,373 filed Jul. 19, 2019 and titled “Methods and Apparatus for Patient Positioning in Magnetic Resonance Imaging,” which claims priority under 35 U.S.C. § 119 to U.S. Provisional Application Ser. No. 62/700,711 filed Jul. 19, 2018 and titled “Methods and Apparatus for Patient Positioning in Magnetic Resonance Imaging,” and U.S. Provisional Application Ser. No. 62/811,361 filed Feb. 27, 2019 and titled “Methods and Apparatus for Patient Positioning in Magnetic Resonance Imaging,” each application of which is herein incorporated by reference in its entirety.
BACKGROUNDMagnetic resonance imaging (MRI) provides an important imaging modality for numerous applications and is widely utilized in clinical and research settings to produce images of the inside of the human body. As a generality, MRI is based on detecting magnetic resonance (MR) signals, which are electromagnetic waves emitted by atoms in response to state changes resulting from applied electromagnetic fields. For example, nuclear magnetic resonance (NMR) techniques involve detecting MR signals emitted from the nuclei of excited atoms upon the re-alignment or relaxation of the nuclear spin of atoms in an object being imaged (e.g., atoms in the tissue of the human body). Detected MR signals may be processed to produce images, which in the context of medical applications, allows for the investigation of internal structures and/or biological processes within the body for diagnostic, therapeutic and/or research purposes.
MRI provides an attractive imaging modality for biological imaging due to the ability to produce non-invasive images having relatively high resolution and contrast without the safety concerns of other modalities (e.g., without needing to expose the subject to ionizing radiation, e.g., x-rays, or introducing radioactive material to the body). Additionally, MRI is particularly well suited to provide soft tissue contrast, which can be exploited to image subject matter that other imaging modalities are incapable of satisfactorily imaging. Moreover, MR techniques are capable of capturing information about structures and/or biological processes that other modalities are incapable of acquiring. However, there are a number of drawbacks to MRI that, for a given imaging application, may involve the relatively high cost of the equipment, limited availability and/or difficulty in gaining access to clinical MRI scanners and/or the length of the image acquisition process.
The trend in clinical MRI has been to increase the field strength of MRI scanners to improve one or more of scan time, image resolution, and image contrast, which, in turn, continues to drive up costs. The vast majority of installed MRI scanners operate at 1.5 or 3 tesla (T), which refers to the field strength of the main magnetic field B0. A rough cost estimate for a clinical MRI scanner is approximately one million dollars per tesla, which does not factor in the substantial operation, service, and maintenance costs involved in operating such MRI scanners.
Additionally, conventional high-field MRI systems typically require large superconducting magnets and associated electronics to generate a strong uniform static magnetic field (B0) in which an object (e.g., a patient) is imaged. The size of such systems is considerable with a typical MRI installment including multiple rooms for the magnet, electronics, thermal management system, and control console areas. The size and expense of MRI systems generally limits their usage to facilities, such as hospitals and academic research centers, which have sufficient space and resources to purchase and maintain them. The high cost and substantial space requirements of high-field MRI systems results in limited availability of MRI scanners. As such, there are frequently clinical situations in which an MRI scan would be beneficial, but due to one or more of the limitations discussed above, is not practical or is impossible, as discussed in further detail below.
SUMMARYSome embodiments include a patient handling apparatus configured to facilitate positioning a patient within a magnetic resonance imaging device, the patient handling apparatus comprising a patient support having a surface adapted to be positioned between the patient and a bed so that, when positioned, the surface of the patient support is underneath at least a portion of the patient's body, and a securing portion comprising at least one first releasable securing mechanism configured to engage with a radio frequency component to secure the radio frequency component to the securing portion, and at least one second releasable securing mechanism configured to engage with the magnetic resonance imaging device to secure the securing portion to the magnetic resonance imaging device.
Some embodiment include a helmet configured to accommodate a patient's head during magnetic resonance imaging, the helmet comprising at least one radio frequency transmit and/or receive coil, and at least one first releasable securing mechanism configured to engage with a member attached to a magnetic resonance imaging system at a location such that, when the at least one securing mechanism engages with the member, the helmet is positioned within the imaging region of the magnetic resonance imaging system.
Some embodiments include a helmet configured to accommodate a patient's head during magnetic resonance imaging, the helmet comprising at least one radio frequency transmit and/or receive coil, at least one first releasable securing mechanism configured to engage with a member of the magnetic resonance imaging system such that, when the at least one securing mechanism engages with the member, the at least one securing mechanism resists translation of the helmet relative to the cooperating member, and at least one second securing mechanism configured to, when engaged with a cooperating portion of the member, prevent rotation of the helmet about the member.
Some embodiments include a magnetic resonance imaging system capable of imaging a patient at least partially supported by a support comprising ferromagnetic material, the magnetic resonance imaging system comprising at least one first B0 magnet to produce a first magnetic field to contribute to a B0 magnetic field for the magnetic resonance imaging system, the B0 magnetic field having a field strength of less than or equal to 0.2 T, at least one second B0 magnet to produce a second magnetic field to contribute to the B0 magnetic field for the magnetic resonance imaging system, wherein the at least one first B0 magnet and the at least one second B0 magnet are arranged relative to one another so that an imaging region is provided there between, and a member configured to engage with a releasable securing mechanism of a radio frequency coil apparatus, the member attached to the magnetic resonance imaging between the at least one first B0 magnet and the at least one second B0 magnet at a location so that, when the member is engaged with the releasable securing mechanism of the radio frequency coil apparatus, the radio frequency coil apparatus is secured to the magnetic resonance imaging system substantially within the imaging region.
Some embodiments include a magnetic resonance imaging system capable of imaging a patient at least partially supported by a support comprising ferromagnetic material, the magnetic resonance imaging system comprising at least one first B0 magnet to produce a first magnetic field to contribute to a B0 magnetic field for the magnetic resonance imaging system, the B0 magnetic field having a field strength of less than or equal to 0.2 T, at least one second B0 magnet to produce a second magnetic field to contribute to the B0 magnetic field for the magnetic resonance imaging system, wherein the at least one first B0 magnet and the at least one second B0 magnet are arranged relative to one another so that an imaging region is provided there between, and a member configured to engage with a releasable securing mechanism of a patient handling apparatus configured to secure a radio frequency coil apparatus, the member attached to the magnetic resonance imaging between the at least one first B0 magnet and the at least one second B0 magnet at a location so that, when the member is engaged with the releasable securing mechanism of the patient handling apparatus, the radio frequency coil secured to the patient handling apparatus is positioned substantially within the imaging region.
Some embodiments include a method, comprising releasably securing a support to a magnetic resonance imaging device so as to facilitate magnetic resonance imaging of a patient, the support disposed between the patient and a standard medical bed.
Some embodiments include a method comprising positioning a portion of anatomy of a patient within an imaging region of a magnetic resonance imaging system while the patient is at least partially supported by a standard medical bed, and acquiring at least one magnetic resonance image of the portion of the anatomy of the patient while the patient is at least partially supported by the standard medical bed.
Some embodiments include an apparatus for imaging a foot, the apparatus comprising at least one housing configured to accommodate a patient's foot during magnetic resonance imaging, at least one radio frequency transmit and/or receive coil, and at least one first releasable securing mechanism configured to engage with a member attached to a magnetic resonance imaging system at a location such that, when the at least one securing mechanism engages with the member, the apparatus is positioned within the imaging region of the magnetic resonance imaging system.
Some embodiments include an apparatus for imaging a foot, the apparatus comprising at least one radio frequency transmit and/or receive coil, and at least one housing configured to accommodate a patient's foot during magnetic resonance imaging, the at least one housing tilted at an angle relative to a vertical axis
Some embodiments include a bridge adapted for attachment to a magnetic resonance imaging system and configured to facilitate positioning a patient within the magnetic resonance imaging system, the bridge comprising a support having a surface configured to support at least a portion of the patient, the support being moveable between an up position and a down position, wherein the surface is substantially vertical in the up position and substantially horizontal in the down position, a hinge configured to allow the support to be moved from the up position to the down position and vice versa, and a base configured to attach the bridge to the magnetic resonance imaging system.
Some embodiments include a magnetic resonance imaging system comprising a B0 magnet configured to generate a magnetic field suitable for magnetic resonance imaging, a conveyance mechanism configured to allow the magnetic resonance imaging system to be moved to different locations, and a bridge configured to facilitate positioning a patient within the magnetic resonance imaging system, the bridge comprising a support having a surface configured to support at least a portion of the patient, the support being moveable between an up position and a down position, wherein the surface is substantially vertical in the up position and substantially horizontal in the down position, a hinge configured to allow the support to be moved from the up position to the down position and vice versa, and a base attaching the bridge to the magnetic resonance imaging system.
Some embodiments include a method of imaging a portion of anatomy of a patient while the patient is at least partially supported by a standard medical bed, the method comprising positioning a magnetic resonance imaging system and the bed proximate one another, moving a bridge attached to the magnetic resonance imaging system from a vertical position to a horizontal position so that the bridge overlaps a portion of the bed, positioning the patient via the bridge so that the portion of anatomy of the patient is within an imaging region of the magnetic resonance imaging system, and acquiring at least one magnetic resonance image of the portion of the anatomy of the patient while the patient is at least partially supported by the bed and at least partially supported by the bridge.
Various aspects and embodiments of the disclosed technology will be described with reference to the following figures. It should be appreciated that the figures are not necessarily drawn to scale.
The MRI scanner market is overwhelmingly dominated by high-field systems, and particularly for medical or clinical MRI applications. As discussed above, the general trend in medical imaging has been to produce MRI scanners with increasingly greater field strengths, with the vast majority of clinical MRI scanners operating at 1.5 T or 3 T, with higher field strengths of 7 T and 9 T used in research settings. As used herein, “high-field” refers generally to MRI systems presently in use in a clinical setting and, more particularly, to MRI systems operating with a main magnetic field (i.e., a B0 field) at or above 1.5 T, though clinical systems operating between 0.5 T and 1.5 T are often also characterized as “high-field.” Field strengths between approximately 0.2 T and 0.5 T have been characterized as “mid-field” and, as field strengths in the high-field regime have continued to increase, field strengths in the range between 0.5 T and 1 T have also been characterized as mid-field. By contrast, “low-field” refers generally to MRI systems operating with a B0 field of less than or equal to approximately 0.2 T, though systems having a B0 field of between 0.2 T and approximately 0.3 T have sometimes been characterized as low-field as a consequence of increased field strengths at the high end of the high-field regime. Within the low-field regime, low-field MRI systems operating with a B0 field of less than 0.1 T are referred to herein as “very low-field” and low-field MRI systems operating with a B0 field of less than 10 mT are referred to herein as “ultra-low field.”
As discussed above, conventional MRI systems require specialized facilities. An electromagnetically shielded room is required for the MRI system to operate and the floor of the room must be structurally reinforced. Additional rooms must be provided for the high-power electronics and the scan technician's control area. Secure access to the site must also be provided. In addition, a dedicated three-phase electrical connection must be installed to provide the power for the electronics that, in turn, are cooled by a chilled water supply. Additional HVAC capacity typically must also be provided. These site requirements are not only costly, but significantly limit the locations where MRI systems can be deployed. Conventional clinical MRI scanners also require substantial expertise to both operate and maintain. These highly trained technicians and service engineers add large on-going operational costs to operating an MRI system. Conventional MRI, as a result, is frequently cost prohibitive and is severely limited in accessibility, preventing MRI from being a widely available diagnostic tool capable of delivering a wide range of clinical imaging solutions wherever and whenever needed. Typically, patient must visit one of a limited number of facilities at a time and place scheduled in advance, preventing MRI from being used in numerous medical applications for which it is uniquely efficacious in assisting with diagnosis, surgery, patient monitoring and the like.
As discussed above, high-field MRI systems require specially adapted facilities to accommodate the size, weight, power consumption and shielding requirements of these systems. For example, a 1.5 T MRI system typically weighs between 4-10 tons and a 3 T MRI system typically weighs between 8-20 tons. In addition, high-field MRI systems generally require significant amounts of heavy and expensive shielding. Many mid-field scanners are even heavier, weighing between 10-20 tons due, in part, to the use of very large permanent magnets and/or yokes. Commercially available low-field MRI systems (e.g., operating with a B0 magnetic field of 0.2 T) are also typically in the range of 10 tons or more due to the large amounts of ferromagnetic material used to generate the B0 field, with additional tonnage in shielding. To accommodate this heavy equipment, rooms (which typically have a minimum size of 30-50 square meters) have to be built with reinforced flooring (e.g., concrete flooring), and must be specially shielded to prevent electromagnetic radiation from interfering with operation of the MRI system. Thus, available clinical MRI systems are immobile and require the significant expense of a large, dedicated space within a hospital or facility, and in addition to the considerable costs of preparing the space for operation, require further additional on-going costs in expertise in operating and maintaining the system.
In addition, currently available MRI systems typically consume large amounts of power. For example, common 1.5 T and 3 T MRI systems typically consume between 20-40 kW of power during operation, while available 0.5 T and 0.2 T MRI systems commonly consume between 5-20 kW, each using dedicated and specialized power sources. Unless otherwise specified, power consumption is referenced as average power consumed over an interval of interest. For example, the 20-40 kW referred to above indicates the average power consumed by conventional MRI systems during the course of image acquisition, which may include relatively short periods of peak power consumption that significantly exceeds the average power consumption (e.g., when the gradient coils and/or RF coils are pulsed over relatively short periods of the pulse sequence). Intervals of peak (or large) power consumption are typically addressed via power storage elements (e.g., capacitors) of the MRI system itself. Thus, the average power consumption is the more relevant number as it generally determines the type of power connection needed to operate the device. As discussed above, available clinical MRI systems must have dedicated power sources, typically requiring a dedicated three-phase connection to the grid to power the components of the MRI system. Additional electronics are then needed to convert the three-phase power into single-phase power utilized by the MRI system. The many physical requirements of deploying conventional clinical MRI systems creates a significant problem of availability and severely restricts the clinical applications for which MRI can be utilized.
Accordingly, the many requirements of high-field MRI render installations prohibitive in many situations, limiting their deployment to large institutional hospitals or specialized facilities and generally restricting their use to tightly scheduled appointments, requiring the patient to visit dedicated facilities at times scheduled in advance. Thus, the many restrictions on high field MRI prevent MRI from being fully utilized as an imaging modality. Despite the drawbacks of high-field MRI mentioned above, the appeal of the significant increase in SNR at higher fields continues to drive the industry to higher and higher field strengths for use in clinical and medical MRI applications, further increasing the cost and complexity of MRI scanners, and further limiting their availability and preventing their use as a general-purpose and/or generally-available imaging solution.
The low SNR of MR signals produced in the low-field regime (particularly in the very low-field regime) has prevented the development of a relatively low cost, low power and/or portable MRI system. Conventional “low-field” MRI systems operate at the high end of what is typically characterized as the low-field range (e.g., clinically available low-field systems have a floor of approximately 0.2 T) to achieve useful images. Though somewhat less expensive than high-field MRI systems, conventional low-field MRI systems share many of the same drawbacks. In particular, conventional low-field MRI systems are large, fixed and immobile installments, consume substantial power (requiring dedicated three-phase power hook-ups) and require specially shielded rooms and large dedicated spaces. The challenges of low-field MRI have prevented the development of relatively low cost, low power and/or portable MRI systems that can produce useful images.
The inventors have developed techniques enabling portable, low-field, low power and/or lower-cost MRI systems that can improve the wide-scale deployability of MRI technology in a variety of environments beyond the current MRI installments at hospitals and research facilities. As a result, MRI can be deployed in emergency rooms, small clinics, doctor's offices, in mobile units, in the field, etc. and may be brought to the patient (e.g., bedside) to perform a wide variety of imaging procedures and protocols. Some embodiments include very low-field MRI systems (e.g., 0.1 T, 50 mT, 20 mT, etc.) that facilitate portable, low-cost, low-power MRI, significantly increasing the availability of MRI in a clinical setting.
There are numerous challenges to developing a clinical MRI system in the low-field regime. As used herein, the term clinical MRI system refers to an MRI system that produces clinically useful images, which refers to images having sufficient resolution and adequate acquisition times to be useful to a physician or clinician for its intended purpose given a particular imaging application. As such, the resolutions/acquisition times of clinically useful images will depend on the purpose for which the images are being obtained.
Among the numerous challenges in obtaining clinically useful images in the low-field regime is the relatively low SNR. Specifically, the relationship between SNR and B0 field strength is approximately B05/4 at field strength above 0.2 T and approximately B03/2 at field strengths below 0.1 T. As such, the SNR drops substantially with decreases in field strength with even more significant drops in SNR experienced at very low field strength. This substantial drop in SNR resulting from reducing the field strength is a significant factor that has prevented development of clinical MRI systems in the very low-field regime. In particular, the challenge of the low SNR at very low field strengths has prevented the development of a clinical MRI system operating in the very low-field regime. As a result, clinical MRI systems that seek to operate at lower field strengths have conventionally achieved field strengths of approximately the 0.2 T range and above. These MRI systems are still large, heavy and costly, generally requiring fixed dedicated spaces (or shielded tents) and dedicated power sources.
The inventors have developed low-field and very low-field MRI systems capable of producing clinically useful images, allowing for the development of portable, low cost and easy to use MRI systems not achievable using state of the art technology. According to some embodiments, an MRI system can be transported to the patient to provide a wide variety of diagnostic, surgical, monitoring and/or therapeutic procedures, generally, whenever and wherever needed. There are challenges to providing an MRI system that can be transported to the patient and/or operated outside specialized facilities (e.g., outside secure and shielded rooms), a number of which are addressed using the techniques described in U.S. patent Ser. No. 10/222,434 (hereinafter, “the '434 patent”), titled “Portable Magnetic Resonance Imaging Methods and Apparatus,” issued Mar. 5, 2019, which patent is herein incorporated by reference in its entirety.
Another challenge involves positioning the patient within the MRI system for imaging. As discussed above, conventional MRI is confined to specialized facilities, including a room for the device itself that is outfitted with extensive shielding and must meet stringent safety regulations, including requiring the room to be secure and free from ferrous material due to the high field strengths involved in conventional clinical MRI. Standard hospital beds are constructed using ferrous material, often steel, prohibiting there use with conventional clinical MRI systems. As a result, a patient must be brought to the specialized facility dedicated to the MRI system and transferred to a custom bed designed for use with the MRI system.
For patients that are ambulatory, this may mean requiring the patient to enter the secure room housing the MRI device and positioning themselves on a MRI-safe bed integrated with the MRI device. For patients that are not ambulatory or are otherwise immobilized, the patient may need to be first transferred to a customized MRI-safe bed to be transported to the secure room and then transferred to the integrated bed of the MRI system. Such requirements limit the circumstances in which a patient can undergo MRI and in some cases prohibits the use of MRI entirely. For example, transfer of non-ambulatory and/or immobile patients to an MRI safe bed or wheel chair to transport the patient into the secure room and, potentially, another transfer to the integrated bed or patient support of the MRI system is difficult and, in some circumstances, not feasible for medical safety reasons. Additionally, MRI safe beds are costly and not widely available.
The inventors have developed techniques that allow MRI to be performed in conjunction with a standard patient support, such as a standard hospital bed or standard wheelchair, thereby eliminating the requirement of transferring patients one or more times, as well eliminating costs and availability issues associated with specialized MRI safe transports (e.g., beds, wheelchairs, etc.). Additionally, techniques that allow MRI to be performed, for example, from a standard hospital bed, facilitate point-of-care MRI. According to some embodiments, MRI is performed at field strengths that are low enough to allow for imaging to be performed on a patient positioned on or in a standard patient support, for example, a patient lying on a standard hospital bed or seated in a standard wheelchair. As used herein, a standard hospital bed or standard wheelchair refers to a patient support that has not been outfitted for use with conventional high-field MRI. Standard hospital beds or wheelchairs will often be constructed of ferromagnetic material, such as steel, that prevents there use with high-field MRI.
To image a patient from, for example, a standard hospital bed, certain MRI imaging procedures may require positioning target anatomy of the patient within an MRI system moved to a location, for example, the bed on which the patient is currently lying. The inventors have developed techniques for facilitating the positioning of a patient within an MRI system for imaging of desired anatomy of the patient. According to some embodiments, a patient handling system that can be secured to the MRI system is used to support the patient and position the desired anatomy of the patient within the MRI system.
Conventional MRI systems typically include an integrated bed or support for the patient that is constructed using non-ferrous material to satisfy stringent regulatory requirements (e.g., regulations promulgated to ensure both patient and clinician safety) and so as to not disturb the magnetic fields produced by the MRI system. This customized MRI-safe bed is generally configured to be slid into and out of the bore of the system and typically has mounts that allow the appropriate radio frequency coil apparatus to be connected over the portion of the anatomy to be imaged. When preparing a patient for imaging, the patient is positioned on the bed outside the magnet bore so that the radio frequency coil apparatus can be positioned and attached to the cooperating mounts on the bed. For example, for a brain scan, a radio frequency head coil apparatus is positioned about the patient's head and attached to cooperating mounts fixed to the bed. After the radio frequency coil apparatus is attached and positioned correctly, the bed is moved inside the B0 magnet so that the portion of the anatomy being imaged is positioned within the image region of the MRI system.
The inventors have recognized that this conventional process is not applicable to portable or point-of-care MRI, nor can this process be used to image a patient from a standard medical bed or wheelchair. For example, standard medical beds are not equipped with mounts to which a radio frequency coil apparatus can be attached, nor are radio frequency coil apparatus configured to be attached to standard medical beds. In addition, a standard medical bed or wheelchair cannot be positioned within the imaging region of an MRI system. To facilitate imaging from, for example, a standard medical bed, the inventors have developed radio frequency coil apparatus adapted to accommodate target anatomy of a patient and configured to engage with a cooperating member attached to the MRI system so that when the radio frequency coil apparatus is engaged with the member, the target anatomy is positioned within the imaging region of the MRI system. In this way, the radio frequency coil apparatus can be positioned about the patient and then attached to a portable MRI system so that the patient can be imaged from a standard medical bed or wheelchair, allowing the MRI system to be brought to the patient or the patient wheeled to an available MRI system and imaged from the standard medical bed. Such point-of-care MRI allows MRI to be utilized in a wide variety of medical situations where conventional MRI is not available (e.g., in the emergency room, intensive care unit, operating rooms, etc.).
According to some embodiments, a radio frequency helmet comprising one or more radio frequency coils is adapted to accommodate a patient's head. The radio frequency helmet comprises a releasable securing mechanism configured to secure the helmet to a member attached to the MRI system at a location so that whenever the radio frequency helmet is secured to the member, the helmet is substantially within the imaging region of the MRI system. In particular, when the helmet accommodates a patient's head and is secured to the member, the patient's head is positioned within the imaging region of the MRI system. According to some embodiments, a radio frequency coil apparatus comprising one or more radio frequency coils adapted to accommodate an appendage, such as a leg or an arm, is equipped with such a releasable securing mechanism so that when the radio frequency coil apparatus is secured to the member, the radio frequency coil apparatus is substantially within the imaging region of the MRI system so that the appendage positioned for imaging.
As illustrated in
Gradient coils 128 may be arranged to provide gradient fields and, for example, may be arranged to generate gradients in the B0 field in three substantially orthogonal directions (X, Y, Z). Gradient coils 128 may be configured to encode emitted MR signals by systematically varying the B0 field (the B0 field generated by magnet 122 and/or shim coils 124) to encode the spatial location of received MR signals as a function of frequency or phase. For example, gradient coils 128 may be configured to vary frequency or phase as a linear function of spatial location along a particular direction, although more complex spatial encoding profiles may also be provided by using nonlinear gradient coils. For example, a first gradient coil may be configured to selectively vary the B0 field in a first (X) direction to perform frequency encoding in that direction, a second gradient coil may be configured to selectively vary the B0 field in a second (Y) direction substantially orthogonal to the first direction to perform phase encoding, and a third gradient coil may be configured to selectively vary the B0 field in a third (Z) direction substantially orthogonal to the first and second directions to enable slice selection for volumetric imaging applications. As discussed above, conventional gradient coils also consume significant power, typically operated by large, expensive gradient power sources, as discussed in further detail below.
MRI is performed by exciting and detecting emitted MR signals using transmit and receive coils, respectively (often referred to as radio frequency (RF) coils). Transmit/receive coils may include separate coils for transmitting and receiving, multiple coils for transmitting and/or receiving, or the same coils for transmitting and receiving. Thus, a transmit/receive component may include one or more coils for transmitting, one or more coils for receiving and/or one or more coils for transmitting and receiving. Transmit/receive coils are also often referred to as Tx/Rx or Tx/Rx coils to generically refer to the various configurations for the transmit and receive magnetics component of an MRI system. These terms are used interchangeably herein. In
Power management system 110 includes electronics to provide operating power to one or more components of the low-field MRI system 100. For example, as discussed in more detail below, power management system 110 may include one or more power supplies, gradient power components, transmit coil components, and/or any other suitable power electronics needed to provide suitable operating power to energize and operate components of MRI system 100. As illustrated in
Power component(s) 114 may include one or more RF receive (Rx) pre-amplifiers that amplify MR signals detected by one or more RF receive coils (e.g., coils 126), one or more RF transmit (Tx) power components configured to provide power to one or more RF transmit coils (e.g., coils 126), one or more gradient power components configured to provide power to one or more gradient coils (e.g., gradient coils 128), and one or more shim power components configured to provide power to one or more shim coils (e.g., shim coils 124).
In conventional MRI systems, the power components are large, expensive and consume significant power. Typically, the power electronics occupy a room separate from the MRI scanner itself. The power electronics not only require substantial space, but are expensive complex devices that consume substantial power and require wall mounted racks to be supported. Thus, the power electronics of conventional MRI systems also prevent portability and affordability of MRI.
As illustrated in
As should be appreciated from the foregoing, currently available clinical MRI systems (including high-field, mid-field and low-field systems) are large, expensive, fixed installations requiring substantial dedicated and specially designed spaces, as well as dedicated power connections. As discussed above, the inventors have developed low power, portable low-field MRI systems that can be deployed in virtually any environment and that can be brought to the patient who will undergo an imaging procedure. In this way, patients in emergency rooms, intensive care units, operating rooms and a host of other locations can benefit from MRI in circumstances where MRI is conventionally unavailable. The exemplary portable MRI systems described below in connection with
B0 magnet 205 may be coupled to or otherwise attached or mounted to base 250 by a positioning mechanism 290, such as a goniometric stage (examples of which are described in the '434 patent), so that the B0 magnet can be tilted (e.g., rotated about its center of mass) to provide an incline to accommodate a patient's anatomy as needed. In
In addition to providing the load bearing structures for supporting the B0 magnet, base 250 also includes an interior space configured to house the electronics 270 needed to operate the portable MRI system 200. For example, base 250 may house the power components to operate the gradient coils (e.g., X, Y and Z) and the RF transmit/receive coils. The inventors have developed generally low power, low noise and low cost gradient amplifiers configured to suitably power gradient coils in the low-field regime, designed to be relatively low cost, and constructed for mounting within the base of the portable MRI system (i.e., instead of being statically racked in a separate room of a fixed installment as is conventionally done). Examples of suitable power components to operate the gradient coils are described in further detail below (e.g., the power components described in connection with
According to some embodiments, the electronics 270 needed to operate portable MRI system 200 consume less than 1 kW of power, in some embodiments, less than 750 W of power and, in some embodiments, less than 500 W of power (e.g., MRI systems utilizing a permanent B0 magnet solution). Techniques for facilitating low power operation of an MRI device are discussed in further detail below. However, systems that consume greater power may also be utilized as well, as the aspects are not limited in this respect. Exemplary portable MRI system 200 illustrated in
Portable MRI system 200 illustrated in
According to some embodiments, conveyance mechanism 280 includes motorized assistance controlled using a controller (e.g., a joystick or other controller that can be manipulated by a person) to guide the portable MRI system during transportation to desired locations. According to some embodiments, the conveyance mechanism comprises power assist means configured to detect when force is applied to the MRI system and to, in response, engage the conveyance mechanism to provide motorized assistance in the direction of the detected force. For example, rail 255 of base 250 illustrated in
Portable MRI system 200 includes slides 260 that provide electromagnetic shielding to the imaging region of the system. Slides 260 may be transparent or translucent to preserve the feeling of openness of the MRI system to assist patients who may experience claustrophobia during conventional MRI performed within a closed bore. Slides 260 may also be perforated to allow air flow to increase the sense of openness and/or to dissipate acoustic noise generated by the MRI system during operation. The slides may have shielding 265 incorporated therein to block electromagnetic noise from reaching the imaging region. According to some embodiments, slides 260 may also be formed by a conductive mesh providing shielding 265 to the imaging region and promoting a sense of openness for the system. Thus, slides 260 may provide electromagnetic shielding that is moveable to allow a patient to be positioned within the system, permitting adjustment by personnel once a patient is positioned or during acquisition, and/or enabling a surgeon to gain access to the patient, etc. Thus, the moveable shielding facilitates flexibility that allows the portable MRI system to not only be utilized in unshielded rooms, but enables procedures to be performed that are otherwise unavailable. Exemplary slides providing varying levels of electromagnetic shielding are discussed in further detail below.
According to some embodiments, a portable MRI system does not include slides, providing for a substantially open imaging region, facilitating easier placement of a patient within the system, reducing the feeling of claustrophobia and/or improving access to the patient positioned within the MRI system (e.g., allowing a physician or surgeon to access the patient before, during or after an imaging procedure without having to remove the patient from the system). As an example,
B0 magnet 322 may be coupled to or otherwise attached or mounted to base 350 to support the B0 magnet. Base 350 includes housing 302 configured to house the electronics needed to operate the portable MRI system 300 (e.g., as described in detail in the '434 patent). To facilitate transporting the system to the point of care, MRI system 300 may include a conveyance mechanism. In
As shown, MRI system 300 may have a maximum horizontal width W that facilitates the maneuverability of the system within the facilities in which the MRI system is used. According to some embodiments, the maximum horizontal dimension of a portable MRI system is in a range between 40 and 60 inches and, more preferably, in a range between 35 and 45 inches. For example, exemplary MRI system 300 has a maximum horizontal width of approximately 40 inches. As a result, MRI system 300 can be brought to locations in which the MRI is needed, including to the bedside of a patient to be imaged. MRI system 300 also includes bridge 373 that is mounted to the MRI system to facilitate positioning a patient within the imaging region of the MRI system. Bridge 373 may be configured to be attached to different locations around the base to allow a patient to be positioned within the imaging region from different directions and/or orientations. According to some embodiments, bridge 373 is attached to the MRI system 300 so that it can be moved around the perimeter of the B0 magnet. According to some embodiments, bridge 373 is configured to be removed and reattached at different locations around the perimeter of the B0 magnet. According to some embodiments, the bridge may be configured to attach to yoke 320, base 350 or any other suitable portion of MRI system 300, as the aspects are not limited in this respect.
The exemplary low-field MRI systems discussed above and in the '434 patent can be used to provide point-of-care MRI, either by bringing the MRI system directly to the patient or bringing the patient to a relatively nearby MRI system (e.g., by wheeling the patient to the MRI system in a standard hospital bed, wheelchair, etc.). To facilitate imaging of patients using the exemplary systems discussed herein, the inventors have developed techniques to allow a patient to be positioned such that the target anatomy is located correctly within the imaging region of the MRI system, including techniques that allow the patient to be positioned from a standard medical bed, wheelchair or other patient support, even when the patient has limited or no mobility (e.g., the patient is unconscious, sedated or anesthetized, or otherwise has limited autonomous motion).
Following below are more detailed descriptions of various concepts related to, and embodiments of, allowing for point-of-care MRI using a portable low-field MRI. It should be appreciated that the embodiments described herein may be implemented in any of numerous ways. Examples of specific implementations are provided below for illustrative purposes only. It should be appreciated that the embodiments and the features/capabilities provided may be used individually, all together, or in any combination of two or more, as aspects of the technology described herein are not limited in this respect.
As used herein, the term standard hospital or medical bed refers generally to any bed that has not been manufactured to be MRI-safe according to regulations for current high-field MRI and/or that has not been customized for use with conventional high-field clinical MRI systems (e.g., manufactured to be free of any ferromagnetic material). Therefore, standard medical or hospital bed includes not only general purpose hospital beds, but also beds that have been configured for specific medical purposes other than customized beds manufactured to be compliant with current regulatory requirements for use with conventional high field MRI. Thus, beds that are constructed of ferrous or ferrite material (e.g., ferromagnetic material such as iron, steel, etc.) or other material prohibited from being used in restricted areas of conventional clinical MRI are considered standard hospital beds, even though they may be customized for specific purposes.
For conventional clinical MRI, exemplary bed 490 may comprise a steel frame 495 so that, in addition to needing to be transported to a dedicated MRI facility, the patient would be need to be transferred to an integrated bed of the MRI system and/or transferred to an MRI safe bed (e.g., a specially made bed using aluminum or other non-magnetic material), or both. Such requirements limit the circumstances in which a patient can undergo MRI and in some cases prohibits the use of MRI entirely. In
In the embodiment illustrated in
Patient handling apparatus 440 comprises a support portion 442 configured to support at least a portion of the patient while the patient is positioned for imaging and a securing portion 445 configured to releasably secure the patient handling apparatus to a radio frequency coil apparatus (e.g., a radio frequency helmet) and to releasably secure the patient handling apparatus to MRI system 400, some embodiments of which are described in further detail below. Securing portion 445 includes at least one releasable securing mechanism configured to secure the patient handling apparatus to a member 429 attached to the MRI system. In the embodiment illustrated in
As discussed in further detail below, securing portion 445 may also include at least one releasable securing mechanism to secure patient handling apparatus 440 to a radio frequency coil apparatus such that when the patient handling apparatus 440 is secured to the radio frequency coil apparatus and to member 429, the radio frequency coil apparatus is positioned at least partially in and, more preferably, substantially within the imaging region of MRI system 400. As a result, when target anatomy of a patient is positioned within the radio frequency coil secured to the patient handling apparatus 400, and the patient handling apparatus 400 is secured to member 429, the target anatomy is positioned within imaging region 415 of MRI system 400 for image acquisition.
As discussed above, patient handling apparatus comprises a support portion 442 configured to support at least a portion of the patient's body to facilitate positioning the patient within the imaging region of the MRI system. Support portion 442 may include a fold or hinge 442a that allows patient handling apparatus to be folded to make the patient handling apparatus more compact, for example, during storage and/or transport and unfolded, for example, during use. Support portion 442 may be constructed from a molded plastic, such as polyethylene or polypropylene. Fold 442a may be a living hinge, a piano hinge, or any other suitable hinge that facilitates the folding of support portion 442. It should be appreciated that support portion 442 may include multiple folds to increase compactness, or may not include a fold at all, as the aspects are not limited in this respect.
As shown in
Securing portion 545 comprises a first releasable securing mechanism 543 configured to engage with a radio frequency coil apparatus to secure the securing portion 545 (and thus the patient handling apparatus) to the radio frequency coil apparatus. In the exemplary embodiment illustrated in
Retention member 543a is configured to allow member 531 to be moved into smaller diameter portion 543b″ (i.e., in a first direction along axis 505a) and to snap into place to retain member 531 in smaller diameter portion 543b″ (i.e., retention member 543a resists movement of member 531 in a second direction along axis 505a out of the smaller diameter portion into the larger diameter portion). Accordingly, once member 531 has been moved from larger diameter portion 543b′ to smaller diameter portion 543b″, smaller diameter portion 543b″ and retention member 543a secure the radio frequency coil apparatus to the securing portion 545. To disengage the radio frequency coil apparatus from securing portion 545 of a patient handling apparatus, a force may be applied against retention mechanism 543a so that retention mechanism 543a moves aside to allow member 531 to be moved into larger diameter portion 543b of keyhole slot 543b so that the radio frequency coil apparatus can be lifted away from securing portion 545. For example, a force applied to the radio frequency coil apparatus in the second direction along axis 505a causes retention mechanism 543b to slip so that member 531 is allowed to slide into the larger diameter portion of the keyhole.
This process of securing a patient handling apparatus to, and releasing it from, a radio frequency helmet, is described in further detail below in connection with
In
As shown in
Neck portion 631b is dimensioned to be sufficiently small so that it can be accommodated by the smaller diameter portion 643b″ of the keyhole slot so that, after foot portion 631a is inserted in the larger portion of the keyhole slot, member 631 can be moved into the smaller diameter portion 643b″. Body portion 631c is dimensioned to be sufficiently large so that it cannot be accommodated by either the smaller or the larger diameter portions of the keyhole slot. Neck portion 631b has height (e.g., its dimension in the direction of arrow 605c) so that when body portion 631c prevents further insertion of member 631 into the keyhole slot (i.e, further movement in the direction of arrow 605c is prevented by body portion 631c), foot portion 631a has been positioned through the large diameter portion of the keyhole slot so that member 631 can be slid into the smaller diameter portion 643b″ to the secured position illustrated in
Referring again to
Securing portion 545 may further comprise a second releasable securing mechanism 547 configured to engage with a magnetic resonance imaging system to secure the securing portion 545 (and thus the patient handling apparatus) to the magnetic resonance imaging system. According to some embodiments, second releasable securing mechanism 547 comprises tapered lead-in portions 547a that allows a member 429 attached to the magnetic resonance imaging system to enter receptacle portion 547e, and comprises retention portions 547b that prevent member 429 from exiting receptacle 547d. Pulls 547d allow a user to retention portions 547b to allow member 549 to exit receptacle 547d. Springs 547c allow the releasable securing mechanism to be actuated, either by utilizing pulls 547d or under the force of member 429 pushing against tapered lead-in portions 547a. It should be appreciated that the underside of member 429 is illustrated in
Force in the direction shown by arrows 505a may be applied by pushing the tapered portions 547a against member 429, thereby compressing springs 547c and opening the securing mechanism to allow member 429 to enter receptacle 547e. After member 429 enters receptacle 547e, springs 547C return to their repose position and retention portions 547b close behind member 429 to secure securing portion 545 of patient handling apparatus 540 to the magnetic resonance imaging system, as illustrated in
To release patient handling apparatus from the magnetic resonance imaging system, a user can apply a force to pulls 547d in the directions shown by arrows 505b and 505b′ to open releasable securing mechanism 547 (e.g., to place releasable securing mechanism 547 in the open position illustrated in
Referring again to
As shown in
As shown in
According to some embodiments, a radio frequency coil apparatus may be configured to be directly secured to an MRI system without first being secured to a patient handling apparatus.
Releasable securing mechanism 735 comprises a receptacle dimensioned to accommodate member 729 and a retention portion 737 configured to resist movement of the cooperating member 729 once the member has been positioned within the receptacle, as shown in
As discussed above, the view in
Exemplary housing 930a may contain electronics 970 that are used in the operation of transmit/receive coils 930a and 930b, though such electronic may be positioned outside the housing, as the aspects are not limited in this respect. Housing 930a may be attached to base 950 comprising a releasable securing mechanism 935 according to any one or more of the techniques described herein to releasably secure helmet 930 to a magnetic resonance imaging system within the imaging region of the system.
As discussed above, techniques for providing a releasable securing mechanism may also be applied to a radio frequency coil apparatus comprising one or more radio frequency coils adapted to accommodate an appendage, such as a leg or an arm, or a portion of an appendage such as an ankle, foot, wrist, hand, etc.
Exemplary foot coil 1030 also comprises an outer housing 1030a to at least partially cover transmit/receive housing(s) 1030t/r and to form a volume 1030c adapted to accommodate a foot. As illustrated in
By angling the foot coil (i.e., tilting the podal axis away from the vertical axis), a longer foot can be accommodated within the imaging region of, for example, the exemplary MRI systems described herein (e.g., MRI systems having the bi-planar configuration shown in
To accommodate even larger feet, the foot coil may additionally be tilted away from the vertical axis in a direction towards the latitudinal axis. That is, the podal axis may be tilted by an angle φ away from the vertical axis 1025 in the direction of latitudinal axis 1043 illustrated in
It should be appreciated that the podal axis may be chosen as desired to suit the needs of the imaging application and/or the patient and multiple foot coils may be manufactured with different podal axes and dimensions to facilitate MRI of a wide variety of feet under differing circumstances and conditions. According to some embodiments, the foot coil is tilted relative to vertical in the direction of the longitudinal axis at an angle between 5 degrees and 60 degrees (i.e., a podal axis with an angle θ between 5 and 60 degrees), more preferably between 15 degrees and 50 degrees and, more preferably between 30 and 45 degrees (e.g., as illustrated by podal axis 1039 for exemplary foot coil 1030 illustrated in
Foot coil 1030 also comprises back portion 1030b that houses the electronics for the foot coil when connected with bottom portion 1030b′. For example, the electronics forming portions of the radio frequency signal chain (e.g., the transmit/receive circuitry) for operating the transmit and receive coils may be housed in back portion 1030b, 1030b′, as discussed in further detail below. Bottom portion 1030b′ further comprises a terminal connection for cable bundle 1076 which carries power, control and/or data (e.g., MR signal data) from the MRI system to the transmit/receive circuitry housed in the back portion. In the embodiment illustrated in
As visible in the view shown in
In the embodiment illustrated in
As discussed above, receive housing 1030r may be configured to fit within transmit housing 1030t. As visible in the view shown in
In the exemplary configuration illustrated in
As shown in
The view in
Exemplary releasable securing mechanism 1035 comprises a circular receptacle portion dimensioned to accommodate the cooperating member attached to the MRI system and a retention portion 1037 configured to resist movement of the cooperating member once the member has been positioned within the receptacle. Exemplary retention portion 1037 comprises two arm portions 1037a and 1037b, respectively forming a portion of the receptacle and configured to grip the cooperating member when positioned within the receptacle. According to some embodiments, arm portions 1037a and 1037b include protrusions 1033a and 1033b, respectively, configured to resist movement of the cooperating member after it has been inserted into the receptacle of releasable securing mechanism 1035. Protrusions 1033a and 1033b comprise respective outward facing sides 1033a′ and 1033b′ and respective inward facing sides 1033a″ and 1033b″ dimensioned to facilitate securing the cooperating member of the MRI system to foot coil 1030.
According to some embodiments, the angle of the outward facing sides of protrusions 1033a and 1033b and the angle of the inward facing sides of the protrusions are configured such that less forced is required to allow the cooperating member to enter into the receptacle of securing mechanism 1035 than is required to allow the cooperating member to exit the receptacle (e.g., it requires less force to engage with the cooperating member than to disengage with the cooperating member). For example, as discussed above in connection with radio frequency helmet 735, the relative angles of the outward and inward facing sides may be selected so that a relatively small force on the outward facing sides is needed to part arm portions 1037a and 1037b to allow the cooperating member to enter the receptacle of releasable securing mechanism 1035 and a larger force on the inward facing sides is needed to part arm portions 1037a and 1037b to allow foot coil 1030 to be released from the cooperating member (e.g., to allow the cooperating member to be released from the receptacle of securing mechanism 1035).
It should be appreciated that protrusions 1033a and 1033b may be dimensioned in any way so that desired forces achieve engaging and disengaging securing mechanism 1035 with the cooperating member, as the aspects are not limited in this respect. Thus, foot coil 1030 can be secured to and released from the MRI system by applying a force in the appropriate direction. That is, securing mechanism 1035 is releasable because following engagement of arm portions 1037a and 1037b with the cooperating member, foot coil 1030 can released by providing sufficient force on the foot coil so that the cooperating member forces the arm portions 1037a and 1037b outward and releases the foot coil from the cooperating member. According to some embodiments, the cooperating member is similar to or the same as member 829 illustrated in
As discussed above, imaging a patient using MRI from, for example, a standard hospital bed typically requires positioning target anatomy of the patient within an MRI system located proximate the hospital bed on which the patient is lying. As discussed in connection with
To bridge the gap between bed 490 and MRI system 100, the MRI system may be equipped with a bridge 473 mounted to MRI system 100 to facilitate positioning patient 199 within the imaging region of MRI system 100. Specifically, bridge 473 provides a surface 474 over which patient 499 can be moved so that the patient's anatomy being imaged (e.g., the patient's head) can be positioned within the imaging region of the MRI system. However, the inventors have recognized that exemplary bridge 473 illustrated in
As illustrated in
The inventors have recognized the benefits of patient support bridge capable of supporting larger and heavier patients and have appreciated the benefits of such a bridge that can accommodate a range of gaps between the MRI system and a patient bed and/or that provide more overlap between the bridge and the bed. Specifically, for patient comfort, safety and/or to facilitate more convenient positioning of a patient, particularly larger and/or heavier patients, it is desirable to equip a portable MRI system with relatively large dimensioned bridges capable of safely supporting a wide range of patients. However, there are a number of issues associated with the design and development of relatively large dimensioned bridges capable of supporting the weight of larger patients.
For example, as mentioned above, larger bridges increase the footprint of the MRI system even further, making it more difficult (or impossible) to transport the MRI system down hallways and to fit the MRI system through the doorways of the health care facilities in which they are deployed. To address the problem of increased footprint for the MRI system, the inventors have developed a fold-out bridge that can be folded-down to facilitate positioning the patient within the imaging region of the MRI system and to support the patient during an imaging procedure and that can be folded-up during transport of the MRI system so that the MRI system can be more easily moved down hallways and through doorways to the patient.
Additionally, providing a bridge capable of safely supporting larger, heavier patients requires robust construction. Typically, such patient supports would be constructed using large amounts of metal material capable of withstanding the significant stresses resulting from supporting the weight of heavier patients. However, significant quantities of metal may negatively impact the operation of the magnetic resonance imaging system to which the bridge is attached by distorting the main magnetic field and/or producing substantial eddy currents during operation of the magnetic resonance imaging system that negatively impact image quality. To mitigate this problem, some embodiments include a fold-up bridge in which the metal composition of the bridge is minimized to the extent possible to provide a bridge capable of supporting heavier patient while minimizing the impact on the operation of the magnetic resonance imaging system. Thus, the exemplary fold-up bridges described herein may be capable of supporting large and/or heavy patients safely and securely, thus taking advantage of the benefits of larger dimensioned bridges without significantly impacting the ability to move the MRI system down hallways and through doorways.
Following below are more detailed descriptions of various concepts related to, and embodiments of, a fold-out bridge that can be moved from a vertical position for stowing during transport of a portable low-field MRI system or when the MRI system is not in use to a horizontal position to facilitate positioning of the patient for point-of-care MRI. It should be appreciated that the embodiments described herein may be implemented in any of numerous ways. Examples of specific implementations are provided below for illustrative purposes only. It should be appreciated that the embodiments and the features/capabilities provided may be used individually, all together, or in any combination of two or more, as aspects of the technology described herein are not limited in this respect or to the specific combinations described.
When bridge 1300 is in the down position, surface 1310a of support 1310 is substantially horizontal to provide support for the patient. Support 1310, and particularly surface 1310a, may be made of material that reduces friction between a patient and the bridge, such as a smooth plastic, to facilitate positioning of the patient within the imaging region of the MRI system without producing eddy currents during operation of the system. As shown in
Bridge 1300 comprises a hinge 1350 that allows support 1310 to pivot from the up position to the down position and vice versa (e.g., hinge 1350 allows bridge 1300 to be moved between the positions illustrated in
Base 1352 further comprises counter-bores 1345 (e.g., bores 1345a, 1345b and 1345c) to accommodate bolts that allow bridge 1300 to be securely attached to the MRI system. For example, according to some embodiments, base 1352 is constructed with three counter-bores to accommodate respective M8 bolts that securely attach the base of the bridge directly to the B0 magnet of the MRI system (e.g., as shown in
As discussed above, the inventors have recognized the benefits of providing a bridge that can accommodate larger (e.g., wider) and heavier patients and that can bridge larger gaps between a patient bed and the MRI system and/or that provide additional overlap with the patient bed when placed in the down position. According to some embodiments, a fold-out bridge is constructed having a width of between 12 and 36 inches and a length of between 8 and 24 inches. For example, exemplary bridge 1300 has a width W of at least 24 inches and a length L of at least 12 inches to provide a relatively large surface to accommodate a variety of patients and to bridge a variety of gaps. The length of the bridge refers to the dimension generally in a direction outward from the MRI system. By increasing the length of the bridge, larger gaps can be bridged and/or larger overlaps with a patient bed can be achieved.
The width of the bridge refers to the dimension generally in a direction tangent to the MRI system. By increasing the width of the bridge, wider patients may be more comfortably accommodated and supported. Hospital equipment for acute care is often rated to accommodate patients weighing 500 lbs. (e.g., hospital beds are often rated to support 500 lb. patients). According to some embodiments, bridge 1300 is also rated for 500 lb. patients and may be constructed to have a safety factor of at least 2.5 (i.e., that have a yield strength of at least 2.5 times the rating). According to some embodiments, bridge 1300 is rated for 500 lb. patients and is constructed to have a safety factor of 4.0 or more, examples of which are described in further detail below.
To construct hinge 1350, pivot portion 1358 comprises shoulders 1359a and 1359b between which is provided gap 1363 sized to accommodate base 1352. Shoulders 1359a, 1359b and stop 1354 of base 1352 include cooperating bores 1365 through which shaft 1355 is inserted to allow support 1310 to pivot between the up and down positions. When constructed, shaft 1355 is secured within bores 1365 of the base and pivot portions with nuts 1366a and bolts 1366b at both ends of the shaft. Thus, pivot portion 1358 is allowed to rotate about the shaft so that support 1310 can be moved from the vertical position (i.e., in which planar surface 1310a is substantially vertical) when not in use to the horizontal position (i.e., in which the planar surface 1310a is substantially horizontal) to facilitate positioning a patient within the imaging region of the MRI system and to support the patient during imaging. As discussed above, bridge 1400 can be bolted to the MRI system via bolt holes 1345a-c (e.g., bolted to the lower B0 magnet of the MRI system so that it is level with the patient surface within the imaging region of the MRI system as shown in
Bridge 1400 may further include ball plungers 1380a and 1380b that facilitate holding the bridge in the vertical position when the bridge is not being used. For example, ball or spring plungers 1380a and 1380b may be positioned on either side of base 1352 to interact with shoulders 1359a and 1359b of pivot portion 1358. Specifically, to move bridge 1400 from the vertical to the horizontal position, the shoulders of the pivot portion must first overcome the resistance provided by the spring loaded ball plungers (i.e., to pivot bridge 1400 out of the vertical position, shoulders 1359a and 1359b must first move over the ball plungers, which provide a counter-resistance to the initial rotation of the pivot portion). Accordingly, because an initial force exceeding the resistance of the ball plungers is needed to move the bridge out of the vertical position, a measure of safety is provided by reducing the chances that bridge 1400 will unintentionally fall from the vertical position to the horizontal position. Bridge 1400 may also include rubber stoppers 1393 configured to fit within corresponding holes provided in stop 1353 of base 1352 to reduce noise produced when shoulders 1359a, 1359b contact stop 1353 when the bridge is moved to the down position and/or to absorb some of the impact of the bridge should the bridge fall or if the bridge is roughly handled during transition to the horizontal position.
Bridge 1500 is provided with a support 1310 having a relatively large surface area, for example, a width of 24 inches and a length of 14.4 inches measured from the far side of support 1310 to the center of the curved interface of base 1352 where bridge 1500 is bolted to the MRI system (i.e., at counter-bore 1345b). Support 1310 is formed, at least in part, by a 1 inch thick plastic platform that provides a surface 1310a over which a patient can be moved to position the patient within the MRI system. Similar to the construction of exemplary bridge 1400, pivot portion 1358 is coupled to support 1310 via a tongue-and-groove interface and coupled to the base via a 16 mm diameter shaft 1355 inserted through shoulder portions 1359a and 1359b. For exemplary bridge 1500, shoulders 1359a and 1359b are constructed of metal (e.g., aluminum) and tongue portion 1357 is constructed of plastic (or other non-metallic material). Base 1352 for exemplary bridge 1550 is constructed of metal, such as steel, and comprises three counter-bores 1345a-c for bolting bridge 1500 to the B0 magnet of the MRI system (e.g., using three corresponding M8 bolts). In this way, components of bridge 1500 that undergo the greatest amount of stress may be constructed of metal and components that undergo less stress may be made of plastic (or other non-metallic material) to minimize eddy current production when the MRI system is operated, while providing a bridge with a robust construction.
To evaluate the performance of exemplary bridge 1500, stress tests were simulated on the model of bridge 1500 to ensure that the design achieves a 500 lb. rating with a safety factor suitable for patient support equipment. In particular, using the above described construction details, a mesh was applied to the model of bridge 1500 as shown in
Figure A.19 of IEC 60601-1, which is reproduced herein as
To evaluate bridge 1500 for a 500 lb. rating, the stresses on bridge 1500 resulting from a 500 lb. patient were simulated by distributing 250 lbs. of weight over the surface of the bridge (i.e., 50% of the patient's weight that the bridge needs to support), as shown by the downward arrows in
The inventors have recognized that some embodiments of a fold-out bridge may be relatively large and heavy, particularly when dimensioned and constructed to facilitate positioning and support of larger, heavier patients. For example, an exemplary bridge may be dimensioned to have a length of between 1 and 2 feet or more and a width of between 1.5 and 2.5 feet or more, resulting in bridges that can weigh between 8 and 15 lbs. or more. Larger, heavier bridges have the potential to injure if the bridge accidentally falls from the vertical position. To prevent a bridge from being able to free fall, the inventors have developed a counter-balance mechanism configured to slow the rate at which the bridge can transition from the up position to the down position. The counter-balance mechanism provides an additional safety precaution that protects patients and medical personnel from possible injury, as discussed in further detail below.
In particular, end portions 1376a are arranged in the direction of the axis of shaft 1655 and positioned on the perimeter of the respective torsion spring and are configured to fit into a corresponding indexing hole 1378 provided in indexing components 1377a, 1377b. End portions 1376b are similarly arranged and configured to fit into respective indexing holes 1378 provided in shoulders 1659a and 1659b of pivot portion 1658. Specifically, indexing components 1377a, 1377b comprise a plurality of indexing holes 1378 around the perimeter (see e.g., exemplary indexing holes 1378a and 1378b illustrated in
Shaft 1655 includes flats 1655a and 1655b configured to fit into respective indexing components 1377a and 1377b. Specifically, flats 1655a and 1655b are configured to be inserted into slots 1379 provided in respective indexing components 1377a, 1377b (as seen best in the magnified view shown in
When constructed as described above, shaft 1655 is fixed in place and prevented from rotating by inserting the shaft through bores 1365 and into slots 1379 of the respective indexing portions 1377a, 1377b and screwing the shaft in place via screws 1666a, 1666b and 1335. By inserting end portions 1376a and 1376b of the torsion springs 1375a, 1375b into the indexing portions 1377a, 1377b and pivot portion 1658, respectively, rotation of pivot portion 1658 from the vertical position to the horizontal position causes the torsion springs to tighten due to the fixed connection between end portions 1376a and the indexing components 1377a, 1377b (which does not rotate) and the fixed connection between end portions 1376b and the indexing holes 1378c, 1378d in notches 1656a, 1656b, respectively, by which end portions 1376b are rotated along with the pivot portion 1658. That is, because indexing holes 1378c and 1378d and end portions 1376b are aligned in the direction of the shaft axis but are positioned off-axis, the rotation of the pivot portion causes the torsion spring to tighten as indexing holes 1378c and 1378d rotate about the axis of the shaft. Thus, when the bridge pivots from a vertical to a horizontal position, the twisting of the torsion springs slows the rotation of support 1310 to prevent the bridge from rotating in free fall. The spring constant of the torsion springs can be selected to achieve the desired level of control of the rate at which the bridge is allowed to transition between the up and down positions. In this manner, bridge 1600 includes a counter-balance mechanism providing an additional safety mechanism to reduce the chances of injury when using a fold-out bridge.
As discussed above, the exemplary fold-out bridges described herein are configured to attach to a portable magnetic resonance imaging system to facilitate positioning and supporting a patient during point-of-care MRI.
In particular, to facilitate transporting portable MRI system 10000 to locations at which MRI is needed, portable MRI system 10000 is equipped with a fold-out bridge 1700, which may include any one or more of the features of a fold-out bridge described herein.
As discussed above, portable MRI system 10000 includes a conveyance mechanism configured to allow the portable MRI system to be transported to desired locations. Referring to
According to some embodiments, conveyance mechanism 10080 includes motorized assistance controlled using a controller (e.g., a joystick or other controller that can be manipulated by a person) to guide the portable MRI system during transportation to desired locations. According to some embodiments, the conveyance mechanism comprises power assist means configured to detect when force is applied to the MRI system and to engage the conveyance mechanism to provide motorized assistance in the direction of the detected force. For example, rail 10050 illustrated in
Thus, low-field MRI system 10000 equipped with fold-out bridge 1700 can be used to perform point-of-care MRI on a patient, including large and heavy patients. For example, to perform point-of-care MRI on a patient from a standard medical bed, the MRI system and the bed can be positioned proximate one another. In some embodiments, the MRI system is portable and can be moved into position near the hospital bed by medical personnel pushing the MRI system into place and/or using a motor drive conveyance system to move the MRI system into position. In some instances, the MRI system may need to be transported from another room or unit within the hospital. In other instances, the MRI system may already be located in the same room as the patient and need only be moved next to the bed of the patient. In other circumstances, a hospital bed is transported to the MRI system and moved into place proximate the MRI system for imaging. During the positioning of the MRI system and the patient bed near one another, a fold-out bridge attached to the MRI system may be positioned in the vertical or up position (e.g., in the vertical position illustrated in
Once the MRI system and the bed are positioned proximate one another, the fold-out bridge may be moved from the vertical position to a horizontal position so that the bridge at least partially overlaps the bed (e.g., the fold-out bridge 1700 may be moved from the vertical position illustrated in
Having thus described several aspects and embodiments of the technology set forth in the disclosure, it is to be appreciated that various alterations, modifications, and improvements will readily occur to those skilled in the art. Such alterations, modifications, and improvements are intended to be within the spirit and scope of the technology described herein. For example, those of ordinary skill in the art will readily envision a variety of other means and/or structures for performing the function and/or obtaining the results and/or one or more of the advantages described herein, and each of such variations and/or modifications is deemed to be within the scope of the embodiments described herein. Those skilled in the art will recognize, or be able to ascertain using no more than routine experimentation, many equivalents to the specific embodiments described herein. It is, therefore, to be understood that the foregoing embodiments are presented by way of example only and that, within the scope of the appended claims and equivalents thereto, inventive embodiments may be practiced otherwise than as specifically described. In addition, any combination of two or more features, systems, articles, materials, kits, and/or methods described herein, if such features, systems, articles, materials, kits, and/or methods are not mutually inconsistent, is included within the scope of the present disclosure.
The above-described embodiments can be implemented in any of numerous ways. One or more aspects and embodiments of the present disclosure involving the performance of processes or methods may utilize program instructions executable by a device (e.g., a computer, a processor, or other device) to perform, or control performance of, the processes or methods. In this respect, various inventive concepts may be embodied as a computer readable storage medium (or multiple computer readable storage media) (e.g., a computer memory, one or more floppy discs, compact discs, optical discs, magnetic tapes, flash memories, circuit configurations in Field Programmable Gate Arrays or other semiconductor devices, or other tangible computer storage medium) encoded with one or more programs that, when executed on one or more computers or other processors, perform methods that implement one or more of the various embodiments described above. The computer readable medium or media can be transportable, such that the program or programs stored thereon can be loaded onto one or more different computers or other processors to implement various ones of the aspects described above. In some embodiments, computer readable media may be non-transitory media.
The terms “program” or “software” are used herein in a generic sense to refer to any type of computer code or set of computer-executable instructions that can be employed to program a computer or other processor to implement various aspects as described above. Additionally, it should be appreciated that according to one aspect, one or more computer programs that when executed perform methods of the present disclosure need not reside on a single computer or processor, but may be distributed in a modular fashion among a number of different computers or processors to implement various aspects of the present disclosure.
Computer-executable instructions may be in many forms, such as program modules, executed by one or more computers or other devices. Generally, program modules include routines, programs, objects, components, data structures, etc. that perform particular tasks or implement particular abstract data types. Typically the functionality of the program modules may be combined or distributed as desired in various embodiments.
Also, data structures may be stored in computer-readable media in any suitable form. For simplicity of illustration, data structures may be shown to have fields that are related through location in the data structure. Such relationships may likewise be achieved by assigning storage for the fields with locations in a computer-readable medium that convey relationship between the fields. However, any suitable mechanism may be used to establish a relationship between information in fields of a data structure, including through the use of pointers, tags or other mechanisms that establish relationship between data elements.
The above-described embodiments of the present invention can be implemented in any of numerous ways. For example, the embodiments may be implemented using hardware, software or a combination thereof. When implemented in software, the software code can be executed on any suitable processor or collection of processors, whether provided in a single computer or distributed among multiple computers. It should be appreciated that any component or collection of components that perform the functions described above can be generically considered as a controller that controls the above-discussed function. A controller can be implemented in numerous ways, such as with dedicated hardware, or with general purpose hardware (e.g., one or more processor) that is programmed using microcode or software to perform the functions recited above, and may be implemented in a combination of ways when the controller corresponds to multiple components of a system.
Further, it should be appreciated that a computer may be embodied in any of a number of forms, such as a rack-mounted computer, a desktop computer, a laptop computer, or a tablet computer, as non-limiting examples. Additionally, a computer may be embedded in a device not generally regarded as a computer but with suitable processing capabilities, including a Personal Digital Assistant (PDA), a smartphone or any other suitable portable or fixed electronic device.
Also, a computer may have one or more input and output devices. These devices can be used, among other things, to present a user interface. Examples of output devices that can be used to provide a user interface include printers or display screens for visual presentation of output and speakers or other sound generating devices for audible presentation of output. Examples of input devices that can be used for a user interface include keyboards, and pointing devices, such as mice, touch pads, and digitizing tablets. As another example, a computer may receive input information through speech recognition or in other audible formats.
Such computers may be interconnected by one or more networks in any suitable form, including a local area network or a wide area network, such as an enterprise network, and intelligent network (IN) or the Internet. Such networks may be based on any suitable technology and may operate according to any suitable protocol and may include wireless networks, wired networks or fiber optic networks.
Also, as described, some aspects may be embodied as one or more methods. The acts performed as part of the method may be ordered in any suitable way. Accordingly, embodiments may be constructed in which acts are performed in an order different than illustrated, which may include performing some acts simultaneously, even though shown as sequential acts in illustrative embodiments.
All definitions, as defined and used herein, should be understood to control over dictionary definitions, definitions in documents incorporated by reference, and/or ordinary meanings of the defined terms.
The indefinite articles “a” and “an,” as used herein in the specification and in the claims, unless clearly indicated to the contrary, should be understood to mean “at least one.”
The phrase “and/or,” as used herein in the specification and in the claims, should be understood to mean “either or both” of the elements so conjoined, i.e., elements that are conjunctively present in some cases and disjunctively present in other cases. Multiple elements listed with “and/or” should be construed in the same fashion, i.e., “one or more” of the elements so conjoined. Other elements may optionally be present other than the elements specifically identified by the “and/or” clause, whether related or unrelated to those elements specifically identified. Thus, as a non-limiting example, a reference to “A and/or B”, when used in conjunction with open-ended language such as “comprising” can refer, in one embodiment, to A only (optionally including elements other than B); in another embodiment, to B only (optionally including elements other than A); in yet another embodiment, to both A and B (optionally including other elements); etc.
As used herein in the specification and in the claims, the phrase “at least one,” in reference to a list of one or more elements, should be understood to mean at least one element selected from any one or more of the elements in the list of elements, but not necessarily including at least one of each and every element specifically listed within the list of elements and not excluding any combinations of elements in the list of elements. This definition also allows that elements may optionally be present other than the elements specifically identified within the list of elements to which the phrase “at least one” refers, whether related or unrelated to those elements specifically identified. Thus, as a non-limiting example, “at least one of A and B” (or, equivalently, “at least one of A or B,” or, equivalently “at least one of A and/or B”) can refer, in one embodiment, to at least one, optionally including more than one, A, with no B present (and optionally including elements other than B); in another embodiment, to at least one, optionally including more than one, B, with no A present (and optionally including elements other than A); in yet another embodiment, to at least one, optionally including more than one, A, and at least one, optionally including more than one, B (and optionally including other elements); etc.
Also, the phraseology and terminology used herein is for the purpose of description and should not be regarded as limiting. The use of “including,” “comprising,” or “having,” “containing,” “involving,” and variations thereof herein, is meant to encompass the items listed thereafter and equivalents thereof as well as additional items.
In the claims, as well as in the specification above, all transitional phrases such as “comprising,” “including,” “carrying,” “having,” “containing,” “involving,” “holding,” “composed of,” and the like are to be understood to be open-ended, i.e., to mean including but not limited to. Only the transitional phrases “consisting of” and “consisting essentially of” shall be closed or semi-closed transitional phrases, respectively.
Claims
1-20. (canceled)
21. A magnetic resonance imaging system comprising:
- a B0 magnet configured to produce a B0 magnetic field for the magnetic resonance imaging system, the B0 magnet comprising: at least one first B0 magnet to produce a first magnetic field to contribute to the B0 magnetic field for the magnetic resonance imaging system; and at least one second B0 magnet to produce a second magnetic field to contribute to the B0 magnetic field for the magnetic resonance imaging system; and
- a coupling member attached to the B0 magnet of the magnetic resonance imaging system, such that the coupling member is disposed between the at least one first B0 magnet and the at least one second B0 magnet,
- wherein the coupling member is configured to engage with a securing mechanism of a radio frequency coil apparatus, the securing mechanism for securing the radio frequency coil apparatus to and releasing the radio frequency coil apparatus from the coupling member, so that, when the coupling member is engaged with the securing mechanism of the radio frequency coil apparatus, the radio frequency coil apparatus is secured to the magnetic resonance imaging system.
22. The magnetic resonance imaging system of claim 21, wherein the coupling member is attached to the at least one second B0 magnet.
23. The magnetic resonance imaging system of claim 22, wherein the coupling member comprises a first portion having a first diameter and a second portion having a second diameter larger than the first diameter.
24. The magnetic resonance imaging system of claim 23, wherein the first diameter is selected so that the coupling member can fit within a receptacle of the securing mechanism of the radio frequency coil apparatus.
25. The magnetic resonance imaging system of claim 24, wherein a height of the first portion of the coupling member is configured to allow at least a portion of the securing mechanism forming the receptacle to fit underneath the second portion of the coupling member.
26. The magnetic resonance imaging system of claim 23, wherein the second portion of the coupling member comprises at least one recess configured to accommodate the securing mechanism of the radio frequency coil apparatus to prevent rotation of the radio frequency coil apparatus about the coupling member.
27. The magnetic resonance imaging system of claim 22, wherein the B0 magnetic field has a magnetic field strength of less than or equal to 0.2 Tesla (T) and greater than or equal to 20 mT.
28. The magnetic resonance imaging system of claim 27, wherein the B0 magnetic field has a magnetic field strength of less than or equal to 0.1 T and greater than or equal to 50 mT.
29. The magnetic resonance imaging system of claim 21, wherein the magnetic resonance imaging system is configured to image a patient at least partially supported by a hospital bed comprising ferromagnetic material.
30. The magnetic resonance imaging system of claim 21, further comprising the securing mechanism of the radio frequency coil apparatus.
31. A magnetic resonance imaging system comprising:
- a B0 magnet configured to produce a B0 magnetic field for the magnetic resonance imaging system, the B0 magnet comprising: at least one first B0 magnet to produce a first magnetic field to contribute to the B0 magnetic field for the magnetic resonance imaging system; and at least one second B0 magnet to produce a second magnetic field to contribute to the B0 magnetic field for the magnetic resonance imaging system; and
- a coupling member attached to the B0 magnet of the magnetic resonance imaging system, such that the coupling member is disposed between the at least one first B0 magnet and the at least one second B0 magnet, and
- wherein the coupling member is configured to engage with a securing mechanism of a patient handling apparatus configured to secure to a radio frequency coil apparatus, the securing mechanism for securing the patient handling apparatus to and releasing the patient handling apparatus from the coupling member, so that, when the coupling member is engaged with the securing mechanism of the patient handling apparatus, the radio frequency coil secured to the patient handling apparatus is secured to the magnetic resonance imaging system.
32. The magnetic resonance imaging system of claim 31, wherein the coupling member is attached to the at least one second B0 magnet.
33. The magnetic resonance imaging system of claim 32, wherein the coupling member comprises a first portion having a first diameter and a second portion having a second diameter larger than the first diameter.
34. The magnetic resonance imaging system of claim 33, wherein the first diameter is selected so that the coupling member can fit within a receptacle of the securing mechanism of the patient handling apparatus.
35. The magnetic resonance imaging system of claim 33, wherein a height of the first portion of the coupling member is configured to allow at least a portion of the securing mechanism forming the receptacle to fit underneath the second portion of the coupling member.
36. The magnetic resonance imaging system of claim 31, wherein the B0 magnetic field has a magnetic field strength of less than or equal to 0.2 Tesla (T) and greater than or equal to 20 mT.
37. The magnetic resonance imaging system of claim 36, wherein the B0 magnetic field has a magnetic field strength of less than or equal to 0.1 T and greater than or equal to 50 mT.
38. The magnetic resonance imaging system of claim 31, further comprising the securing mechanism of the patient handling apparatus.
39. A method for facilitating imaging using a magnetic resonance imaging system, the method comprising:
- positioning a portion of anatomy of a patient within the magnetic resonance imaging system; and
- acquiring at least one magnetic resonance image of the portion of the anatomy of the patient while the portion of the anatomy of the patient is within the magnetic resonance imaging system,
- wherein positioning the portion of the anatomy of the patient comprises engaging a securing mechanism of a radio frequency coil apparatus to a coupling member attached to the magnetic resonance imaging system at a location between first and second B0 magnets of the magnetic resonance imaging system, the securing mechanism for securing the radio frequency coil apparatus to the coupling member and releasing the radio frequency coil apparatus from the coupling member, so that, when the coupling member is engaged with the securing mechanism of the radio frequency coil apparatus, the radio frequency coil apparatus is secured to the magnetic resonance imaging system.
40. The method of claim 39, wherein acquiring the at least one magnetic resonance image of the portion of the anatomy of the patient is performed while the patient is at least partially supported by a medical bed comprising at least some ferromagnetic material.
Type: Application
Filed: Apr 6, 2021
Publication Date: Aug 12, 2021
Applicant: Hyperfine Research, Inc. (Guilford, CT)
Inventors: Anne Michele Nelson (Guilford, CT), Christopher Thomas McNulty (Guilford, CT), Jeremy Christopher Jordan (Cromwell, CT), Michael Stephen Poole (Guilford, CT)
Application Number: 17/223,762
