CN101884532A - Superconductive magnetic resonance imager as well as manufacturing method and application - Google Patents
Superconductive magnetic resonance imager as well as manufacturing method and application Download PDFInfo
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Abstract
The invention discloses a superconductive magnetic resonance imager as well as a manufacturing method and application thereof. The superconductive magnetic resonance imager comprises an imaging region, at least one vacuum insulation shield, a main magnet for generating a main magnetic field in the imaging region and a low temperature system connected with the vacuum insulation shield, wherein the vacuum insulation shield is enclosed into a low vacuum region by a sealed high vacuum interlayer, and at least one superconductive radio-frequency coil and a low-temperature heat conducting plate are arranged in the low vacuum region; the superconductive radio-frequency coil is in heat contact with the low-temperature heat conducting plate; and the low-temperature heat conducting plate is connected with the low temperature system through a heat pipe so as to maintain the low temperature required by the superconductive radio-frequency coil. The invention also discloses the manufacturing method of the superconductive magnetic resonance imager. The invention has high signal-to-noise ratio in the imaging region, can improve the utilization efficiency of a clinical magnetic resonance imaging system and is suitable for the imaging of the whole body, the knee, the wrist, the hand, the foot, the neck and the head.
Description
Technical field
The present invention relates to a kind of comprehensive nuclear magnetic resonance (MRI) instrument, particularly relate to a kind of superconducting magnetic resonance imaging device (or title " superconducting magnetic resonance imaging machine ").The invention still further relates to the manufacture method and the application of described superconducting magnetic resonance imaging machine.
Background technology
Nuclear magnetic resonance is a kind of noinvasive imaging of medical technology, is widely used in the clinical and brain function research of medical treatment.Because magnetic resonance imager can carry out imaging to various organizational structuries, particularly to soft tissue owing to the resolution capability that the difference of moisture has, provide useful information to diagnosis.Nearly all human body all is fit to imaging, as nervous system, and musculoskeletal system, cardiovascular system, digestive system and genitourinary system.This technology is to early discovery and treat apoplexy, the Real Time Observation cardiovascular function, and diagnosing tumour and cancer are particularly advantageous.In addition, it is a kind of diagnosis that is used for human and animal's orthopedics injuries and treatment tool of uniqueness; It also can carry out the live body chemical analysis by Spectrum Analysis.
When patient was checked, patient need lie on the sick bed, and the position to be checked of health is placed in the test section (being imaging area) that main Magnet provides.Magnetic field is orientated the hydrogen nuclei in body fluids (proton).Generally, radio frequency (RF) coil and three gradient coils that a room temperature copper material is made are housed in the Magnet.The high-frequency impulse excitation signal that this radio-frequency coil produces produces swaying when fast and magnetizes in human body, the radio frequency magnetic test coil is delivered to computer system with detected wireless signal and carried out imaging.
The application of magnetic field gradient makes powerful magnetic field magnetic field intensity of diverse location in the inspection area that small difference be arranged, thereby different from the frequency of the magnetic resonance signal of different location, can determine by the frequency of signal this signal from the position.
Since invention mr imaging technique in 1977, people are pursuing higher-quality nuclear magnetic resonance always.Equally, in order to reduce the image fog that causes owing to movable body (as blood flow) in patient's motion or the body as far as possible, it also is necessary improving image taking speed.From the angle of contrast and resolution, there is Several Factors to help to improve the magnetic resonance image (MRI) quality.Wherein, a vital parameter, the signal to noise ratio (snr) of signal has determined picture quality.The signal to noise ratio that improves the preamplifier front signal is to improve the key of magnetic resonance imaging system image quality.The definition of signal to noise ratio is the signal and the noise of power ratio, that is:
Signal to noise ratio snr=P
Signal/ P
Noise(formula 1)
Wherein, P
SignalAnd P
NoiseBe respectively the power of signal and noise.
In magnetic resonance imaging system, radio-frequency coil transmitted pulse magnetic excitation hydrogen nuclei (proton) magnetic spin.Meanwhile, receiving coil receives faint free induction signal.For realizing the preferable image quality, the design of the transmitting coil receiving coil that is far from is important.In some cases, same coil is not only as transmitting coil but also as receiving coil, yet ideal transmitting coil and receiving coil have conflict.Therefore, in most of the cases, transmitting coil and receiving coil separate.
Because signal to noise ratio and magnetic field intensity are directly proportional, so an approach that improves signal to noise ratio is to improve the magnetic field intensity of magnet.The unit of measurement magnetic field size is tesla (T) normally, and wherein 1 tesla equals 10000 Gausses.The magnetic field that U.S. FDA (Food and Drug Administration) is given for imaging of medical MRI must not be higher than (the FDA Guidelines for Magnetic ResonanceEquipment Safety of 4 teslas, Center for Devices and Radiological Health, FDA, 2002).
The mode that another kind improves signal to noise ratio is to reduce noise.Having the upper limit owing to be used for the magnetic resonance magnetic field intensity of human body, is a wiser selection so reduce noise.
Noise can be divided into the coil noise that patient's sample noise and receiving coil that health caused are caused.
P
Noise=P
Signal-noise+ P
Coil-noise(formula 2)
Wherein, P
Signal-noiseAnd P
Coil-noiseBe respectively the noise of sample and coil.By formula 1 and formula 2, can obtain signal to noise ratio
SNR=P
Signal/ (P
Signal-noise+ P
Coil-noise) (formula 3)
In formula 3, the size of signal and receiving coil are inversely proportional to the square distance between the sample, and the sample noise is directly proportional with the volume or the visual field of sample.Bigger sample has higher noise.On the other hand, the noise of coil is the function of coil electric conductance, it depends on the material and the temperature (NeilAlford: " Superconducting Receive Coils for a Compact Low Field MRISystem " of receiving coil, in:Physical Electronics and Materials, http://eccel.lsbu.ac.uk/research/pem/MRI.html).
People are having finished number of research projects aspect minimizing sample noise and the coil noise, to improve the picture quality of nuclear magnetic resonance.Yet, even also there is the defective of internal in present state-of-the-art magnetic resonance imaging system.The general magnetic resonance imaging system that is used to scan the whole health of patient has a huge magnet and big receiving coil.Big magnet provides the area that exposes thoroughly that is fit to cover in all sites various tissues.Big receiving coil has very big visual field, but has produced higher sample noise and coil noise simultaneously.In order to shorten the distance between receiving coil and the patient body, to increase signal intensity, patient is often pressed close in the position of receiving coil, magnetic resonance imaging system also tightly be wrapped in patient around.This is the principal element that do not feel well of patient often.In most of the cases, the doctor selects to use dissimilar receiving coils at the organ part of research, as the general purpose table planar coil, and knee joint coil, Breast Coil, head coil, spine coil, coil array etc.Receiving coil can be designed to specific shape, thereby makes it the more approaching organ that is scanned, and improves signal intensity.All radio-frequency coils all are made of such as copper by metal material at present.
The radio-frequency coil of better design and fabrication can be realized high s/n ratio aspect clinical magnetic resonance imaging.Research in the past (HTS Volume Coil with Improved Imaging Volume "; S.Y.Chong; ISMRM; 2008) verified; use superconductor, or specifically, high-temperature superconductor (critical temperature that refers to superconductor here is more than 77K); as YiBaCuO, the superconduction radio-frequency coil of making such as BiSrTiCaO makes the signal to noise ratio of image increase 300-500%.Use the shortcoming of superconduction radio-frequency coil to be, people must use heavy cryogenic system to guarantee the superconducting state of superconduction radio-frequency coil.Up to the present, all high temperature superconductor coil and magnetic resonance imaging systems are isolating.In clinical practice, to often mount and dismount the superconduction radio-frequency coil in order to scan different positions, very trouble.Many designs in the existing general magnetic resonance imaging system, as the superconduction radio-frequency coil, the cryogenic system of superconduction radio-frequency coil, the shell of superconduction radio-frequency coil and sick bed no longer are suitable for new high-performance magnetic resonance imaging system.
Summary of the invention
The technical problem to be solved in the present invention provides a kind of superconducting magnetic resonance imaging machine, and it has high s/n ratio at imaging area, and can improve the utilization ratio of clinical magnetic resonance imaging system; For this reason, the present invention also will provide a kind of manufacture method and application of described superconducting magnetic resonance imaging machine.
For solving the problems of the technologies described above, superconducting magnetic resonance imaging machine of the present invention comprises: imaging area, at least one vacuum insulation cover, the main magnet in imaging area generation magnetic field, a cryogenic system that is connected with the vacuum insulation cover;
The vacuum insulation cover is a double-layer seal fine vacuum interlayer, and the vacuum in its interlayer is 10
-6To 10
-12Between the holder; The vacuum insulation cover surrounds a vacuum 10
-3To 10
-6Coarse vacuum space between the holder;
At least one superconduction radio-frequency coil is installed in the coarse vacuum district, and this superconduction radio-frequency coil provides a described imaging area at vacuum insulation cover near surface;
Low temperature heat-conducting plate in superconduction radio-frequency coil and the coarse vacuum district keeps thermo-contact; The low temperature heat-conducting plate links to each other to keep the superconduction radio-frequency coil to be in required low temperature (referring to 90K or following temperature here) state by a heat pipe with cryogenic system.
Described superconducting magnetic resonance imaging machine can be applicable to whole body, knee, wrist, hands, foot, neck and an imaging.
The method of manufacturing superconducting magnetic resonance imaging machine of the present invention comprises: an imaging area is provided, a patient support system, at least one vacuum insulation cover, a main magnet and a refrigeration system that is installed in the patient support system that is used for producing main field at imaging area;
Build a vacuum pressure between 10
-6To 10
-12Double-layer seal fine vacuum interlayer between the holder; Surround a vacuum pressure between 10 with double-layer seal fine vacuum interlayer
-6To 10
-12Coarse vacuum district between the holder;
A superconduction radio-frequency coil is installed in the coarse vacuum district at least and it is linked to each other with low temperature heat-conducting plate (refer to here operating temperature at 90K or following be mainly used in heat conducting template device); The low temperature heat-conducting plate is linked to each other to keep the required low temperature (referring to 90K or following temperature here) of superconduction radio-frequency coil by a heat pipe with cryogenic system.
In superconducting magnetic resonance imaging machine of the present invention, the superconduction radio-frequency coil is arranged in the superconducting magnetic resonance imaging machine, formed a kind of magnetic resonance imaging system of compact, therefore needn't feel put about for installation and removal superconduction radio-frequency coil, can save the time of changing the superconduction radio-frequency coil, improve the utilization ratio of clinical magnetic resonance imaging system.
The present invention adopts the superconduction radio-frequency coil can improve signal to noise ratio, improves image quality.Under the prerequisite that keeps signal to noise ratio and image quality, adopt superconduction radiofrequency coil technology of the present invention can reduce requirement, thereby significantly reduce the manufacturing cost and the cost of use of magnetic resonance imager main magnets magnetic fields intensity.
In addition, the present invention combines the fine vacuum interlayer with the coarse vacuum district, for the superconduction radio-frequency coil provides insulated heat, has realized a kind of integrated superconducting magnetic resonance imaging system that clinical treatment is used that really is suitable for.
Description of drawings
The present invention is further detailed explanation below in conjunction with accompanying drawing and the specific embodiment:
Fig. 1 is one embodiment of the invention whole body superconducting magnetic resonance imaging machine sketch map.
Fig. 2 is the cutaway view of vacuum insulation cover among Fig. 1.
Fig. 3 is one embodiment of the invention knee imaging system sketch map.
Fig. 4 is one embodiment of the invention wrist imaging system sketch map.
Fig. 5 is a superconduction radio-frequency coil sketch map.
Fig. 6 is an another embodiment of the present invention whole body superconducting magnetic resonance imaging machine sketch map.
The specific embodiment
Can be easy to more complete grasp and understand the present invention by following drawings and detailed description.Following accompanying drawing just briefly introduces, and is disproportionate with material object.
In view of the as above said problem that conventional magnetic resonance imaging system exists, it is necessary to design novel special-purpose superconducting magnetic resonance imaging machine.A special-purpose superconducting magnetic resonance imaging machine needs one to be positioned near the imaging area of superconduction radio-frequency coil.According to formula 2, when imaging area reduces, noise level also will reduce.The mini table planar coil can realize higher signal to noise ratio be because their noises of receiving only from a little sample area.The shortcoming of surface coils is less imaging area and spatial inhomogeneities.Bigger coil has bigger and uniform imaging area.Therefore, using a bigger transmitting coil and a less receiving coil, especially superconduction radio-frequency coil is favourable as receiving coil.
Phased matrix table planar coil can overcome the problem of small field of view.Phased matrix table planar coil comprises a plurality of non-interaction radio-frequency coils, its signal to noise ratio and one of them small coil are similar, and the similar (P.B.Roemer to big coil in big visual field, W.A.Edelstein, C.E.Hayes, S.P.Souza, and O.M.Mueller " The NMR phased array; " Magn.Reson.Med.Vol.16, pp192-225,1990).The phased matrix table planar coil that is used to scan extremity can provide the signal to noise ratio more excellent than body coil, and bigger imaging viewing field can be used for joint and vertebra imaging simultaneously.
Another disadvantage of surface coils is the limited perspective depth of organizing.Helmholtz coil is to overcoming this defective, because it obtains signal from the sample both side surface.Two coils have compensated the deficiency of the limited perspective depth of each coil.
The volume of sample, the method for further improving signal to noise ratio is as far as possible near human body radio-frequency coil in reducing the visual field.
In order further to improve signal to noise ratio, the temperature of selecting suitable material manufacture radio-frequency coil and reducing radio-frequency coil is with increase coil electric conductance (minimizing resistance).Copper radio-frequency coil and superconduction radio-frequency coil all can be used in the nuclear magnetic resonance at present.Some researchs are devoted to reduce copper coil thermal noise (H.C.Seton by reducing the radio-frequency coil running temperature, D.M.Bussell, and J.M.S.Hutchison, " ALiquid Helium-Cooled RF Coil and DC SQUID Amplifier for MRI at 0.01T; " Proc.Soc.Mag.Reson., vol.2, p.959,1995) (A.S.Hall, B.Barnard, P.McArthur, D.J.Gilderdale, I.R.Young, and G.M.Bydder, " Investigation of a whole-body receiver coil operating at liquidnitrogen temperatures; " Magn.Reson.Med., vol.7, p.230,1988).The noise power of coil is also referred to as Johnson noise, is to be directly proportional with the product of resistance with temperature.Reduce the temperature of conventional copper radio-frequency coil, can reduce thermal noise (Johnson noise).This radio-frequency coil low temperature radio-frequency coil of being known as, because it is to be installed in the heat-insulating housing, links to each other with cryogenic system and heat is transmitted on the low temperature cold head to guarantee the low temperature state of low temperature radio-frequency coil from the low temperature radio-frequency coil by heat conduction heat pipe or other heat-transfer devices.
Radio-frequency coil normally uses this characteristic quantity of quality factor (Q) to weigh.When the coil noise was occupied an leading position, signal to noise ratio was directly proportional with the square root of Q/T, and wherein, Q is the quality factor of harmonic oscillator or coil, and T is a coil temperature.The Q-value of (about 300K) copper coil is generally hundreds of at ambient temperature.By contrast, the Q-value that operates in the high-temperature superconductor radio-frequency coil under the liquid nitrogen temperature (77K) can increase 2-3 the order of magnitude (J.R.Miller, K.Zhang, Q.Y.Ma, I.K.Mun, K.J.Jung, J.Katz, D.W.Face, and D.J.Kountz " Highsensitivity sodium receiver coils for magnetic resonance imaging " IEEE Trans.Biomedical Engineering.Vol 43, p1997-99,1996).Be appreciated that in the very short nuclear magnetic resonance time be under the vital situation, having more, the superconduction radio-frequency coil of high s/n ratio can be used to reduce imaging time.
Therefore, the method that further reduces radio-frequency coil resistance is to use the superconduction radio-frequency coil of superconductor.The resistance ratio copper of superconductor hangs down several magnitude.Utilizing superconduction is a kind of minimizing radio-frequency coil noise as the radio-frequency coil material, improves the very promising method of signal to noise ratio.Compare with traditional copper radio-frequency coil, high temperature superconducting materia has extremely low-resistivity under liquid nitrogen temperature (77K).Studies show that owing to use superconduction radio-frequency coil magnetic resonance image (MRI) quality to be significantly improved, signal to noise ratio has improved about three times.Therefore, it is believed that the superconduction radio-frequency coil has a high potential in the nuclear magnetic resonance field.For example, United States Patent (USP) 6943550 and United States Patent (USP) 60/537,782 have disclosed high-temperature superconductor radio-frequency coil mr imaging technique.Coil method can be a copper, silver, YBa2Cu307 (yttrium barium copper oxide) thin film or thick film etc.High temperature superconducting materia such as YBCO structure have extremely low resistance (Tc, 89K, yttrium barium copper oxide) under its critical temperature.
Fig. 1 is a superconducting magnetic resonance imaging machine, and it has embodied the present invention at least in one aspect.This superconducting magnetic resonance imaging machine 100 comprises: 110, one removable sick beds 120 of an imaging area, supporting structure 130; Main magnet comprises upper magnet 140 and lower magnet 142; Also comprise cryogenic system 190 (referring to provide operating ambient temperature here is the following refrigerating plant of 77K).It is the uniform magnetic field of 0.1T to 3T that main magnet produces the magnetic field intensity scope at imaging area 110.The magnetic direction of downfield can design on request, for example perpendicular to sick bed, and the magnetic direction of highfield level normally.
Removable sick bed 120 can carry patient and pass in and out imaging area 110.Part sick bed 122 and supporting construction 132 or their part are positioned at main magnet, and part sick bed 122 and supporting construction 132 are to be made by nonmetal and namagnetic substance (as plastics).
Superconduction radio-frequency coil 152 and cryogenic system 190 are designed to and the removable sick bed 120 integrated superioritys that several aspects are arranged.An advantage is, when superconduction radio-frequency coil 152 and removable sick bed 120 were fixed together, it is compact that whole system can design, thereby help superconduction radio-frequency coil 152 near the part imaging area.Will improve signal to noise ratio like this, thereby the better pictures quality is provided.Additional advantage is, because superconduction radio-frequency coil 152 is fixed on the removable sick bed 120, reduced movable part, simplified, made clinical imaging process and environment reliable more and effective owing to change superconduction radio-frequency coil or the needed superconduction radio-frequency coil of patient calibration steps.In addition, embedded cryogenic system makes cooling more effective.
Build integrated superconducting magnetic resonance imaging machine and still have some challenges.Because imaging area is very compact, spatially arranges the cooling system of superconduction radio-frequency coil that great difficulty is arranged.In addition, because imaging area is in high-intensity magnetic field, all parts all must be selected nonmagnetic substance for use.As shown in Figure 1, traditional Refrigeration Technique is no longer suitable.For example: United States Patent (USP) 7015692 has been described a kind of but superconducting magnetic resonance imaging machine of circularly cooling liquid cooling that utilizes, and this method need be replenished refrigerating fluid and is not suitable for clinical.United States Patent (USP) 7408353 has been described another and has been come adiabatic to keep the cryogenic way of superconduction radio-frequency coil with vacuum; Vacuum system uses vacuum pipeline to link to each other with high-vacuum pump.It is very difficult that in fact a vacuum pump is installed in magnetic resonance system, and the gas leakage problem of vacuum system also is difficult to solve in addition.High vacuum system has also increased the difficulty that material is selected to the requirement of the low venting of material.
The invention solves above-mentioned problems.As a special case of the present invention, Fig. 1,2A and 2B have provided a kind of vacuum insulation cover.Be made of high-vacuum fitting 210 from the visible vacuum insulation cover 150 of Fig. 2 A, high-vacuum fitting 210 is that vacuum pressure is 10
-6With 10
-12Double-layer seal fine vacuum interlayer 220 between the holder.A kind of method of making high-vacuum fitting is to water the double-deck case of the mouth of bleeding having of cast glass.The typical thickness 222 of vacuum interlayer is 1 millimeter to 100 millimeters.Earlier high-vacuum fitting 210 is extracted into 10 with vacuum pump
-6With 10
-12Vacuum between the holder, and then the mouth of bleeding sealed up.Here need high-quality vacuum system could guarantee the service life in more than 210 years of high-vacuum fitting.The material of making high-vacuum fitting 210 can be a G10 fiberglass, glass and quartz, and the combination of these materials.Well-known these nonmagnetic substances can not produce any interference to magnetic field at imaging area.
In Fig. 2 A, in the middle of high-vacuum fitting 210, be that a vacuum pressure is 10 equally
-3With 10
-6 Coarse vacuum district 230 between the holder.Other elements of keeping the coarse vacuum district comprise the O RunddichtringO, vacuum packing ring, vacuum grease, perhaps epoxy resin.A vacuum tube 232 links to each other with coarse vacuum district 230 to produce coarse vacuum.230 li at least one superconduction radio-frequency coil 152 has been installed in this coarse vacuum district, and near the imaging area vacuum insulation cover 150 carries out imaging.In conjunction with shown in Fig. 2 B, superconduction radio-frequency coil 152 and low temperature heat-conducting plate 154 keep thermo-contact in coarse vacuum district 230 again.Low temperature heat-conducting plate 154 links to each other with low temperature cold head 260, and low temperature cold head 260 is connected with cryogenic system by heat pipe 160.Low temperature cold head 154 can be used pottery (as aluminium oxide), plastics, crystal (as sapphire), metal, glass and quartzy the making.
Low temperature cold head (low temperature that refers to 90K or following temperature is cold former, and it may be the heat exchanger of cryogenic system) 260 can be made of copper billet.Though metal derby also can produce interference to magnetic field, this interference can be ignored when the enough little and magnetic field of metal derby is lower than 0.1 tesla.
Using the combination in fine vacuum interlayer and coarse vacuum district is favourable as the vacuum insulation cover, and the fine vacuum interlayer provides effective adiabatic function and is convenient to and makes.The coarse vacuum district provides further insulated heat for the superconduction radio-frequency coil.And making the selection of cryogenic heat transfer plate and superconduction radio-frequency coil material become, the use of coarse vacuum is more prone to.
The ultimate principle of superconducting magnetic resonance imaging machine illustrated in figures 1 and 2 and structure can be used for following imaging system: whole body, foot, knee, wrist, hands, neck and head.Fig. 3 A is an example of knee imaging system.Superconducting magnetic resonance imaging machine 300 comprises a main magnet (not showing among Fig. 3) and removable sick bed 320.Similar with removable sick bed 120, cryogenic system 190 and heat pipe (not showing among Fig. 3) also are installed in the removable sick bed 320.Vacuum insulation cover 340 is installed on the removable sick bed 320 and can and shifts out main magnet along with removable sick bed 320 shift-ins.Vacuum insulation cover 340 links to each other by a heat pipe with cryogenic system 190.
Fig. 3 B is a kind of vacuum insulation cover 340.Coarse vacuum district 350 is surrounded by inside and outside fine vacuum interlayer 352,354.Coarse vacuum district 350 at two ends with O type circle, the vacuum packing ring, vacuum grease, or epoxy sealing forms.And leave vacuum and electric connection, and Heat pipe joint.The column type low temperature heat conductive rod 356 that is installed in the coarse vacuum district links to each other with at least one superconduction radio-frequency coil 358.Low temperature heat conductive rod 356 links to each other with cryogenic system by heat pipe.Fine vacuum interlayer 352 intermediary regional 360 is knee imaging areas.
Superconduction radio-frequency coil 358 is installed in last and and the good thermo-contact of low temperature heat conductive rod 356 maintenances of a curved surface (cylinder) in such structure.Superconduction radio-frequency coil 358 is to make with hts band in this device, for example bismuth-strontium-calcium-copper-oxygen (BSCCO).United States Patent (USP) 6943550 is seen in the description of this hts band radio-frequency coil preparation process.The superconduction radio-frequency coil also can be made by high temperature superconductive wire.
Another example is that superconduction radio-frequency coil 358 is made by high-temperature superconducting thin film (only referring to that here critical temperature is at 77K or above superconductor).High-temperature superconducting thin film is to be made by high temperature superconducting materia, as yttrium barium copper oxide (YBCO), and thallium barium calcium copper oxygen (TBCCO), boronation magnesium, or MBization and thing (M is Be, Al, Nb, Mo, Ta, Ti, Hf, a kind of among V and the Cr).Visible " Superconducting MR Surface Coils for Human the Imaging, " Proc.Mag.Res.Medicine of method for preparing the planar high-temperature superconducting thin film, 1,171 (1999) and list of references.Because high-temperature superconducting thin film is that preparation is on the crystal of a lattice constant match, so the low temperature heat-conducting plate of plane helps conduction of heat.Fig. 3 C is another kind of vacuum insulation cover 370, is coarse vacuum district 372 between interior fine vacuum interlayer 374, the outer fine vacuum interlayer 376, is used to the knee imaging.Have at least two low temperature heat-conducting plates 380,382 to be installed on the heat conductor 384 in the coarse vacuum district 372, this heat conductor 384 links to each other with cryogenic system by heat pipe.High-temperature superconducting thin film radio-frequency coil 385,386 is installed on the low temperature heat-conducting plate 380,384.Zone 390 between the low temperature heat-conducting plate 380,384 is knee imaging areas.The superconduction radio-frequency coil is equipped with at least a superconductor, as YBaCuO, and BiSrCaCuO, TlBiCaCuO and boronation magnesium compound.
In another one example of the present invention, a superconduction radio-frequency coil is housed in the vacuum insulation cover at least and links to each other with cryogenic system, be used for hands or wrist imaging.Fig. 4 A is the imaging system of a kind of hands or wrist.Vacuum insulation cover 410 is installed on the support 400 that links to each other with cryogenic system 190 (not shown).This support 400 can shift-in and is shifted out main magnet (not showing among Fig. 4 A).Patient is sitting on the chair and with hands and places (shown in Fig. 4 B) in the imaging area 450 in imaging process.
Fig. 4 B is an example of vacuum insulation cover 410.Inside and outside high vacuum seal cover the 412, the 414th is made up of the sealing cylinder shell of end sealing.This structure can be made with the technology of blow-molded glass and silica ware, and shown in Fig. 4 B, the bleeding point 413 and 415 on the glass shell is sealed up after air is extracted.At least one superconduction radio-frequency coil 420 is installed on the columniform low temperature heat-conducting plate 425, and this low temperature heat-conducting plate 425 is installed in the coarse vacuum district 440 between the inside and outside high vacuum seal cover 412,414.Low temperature heat-conducting plate 425 links to each other with cryogenic system (not showing among Fig. 4 B) by heat pipe.Maintain a certain distance by adiabatic support between low temperature heat-conducting plate 425 and the inside and outside high vacuum seal cover 412,414.The opening in coarse vacuum district 440 is sealed by O type circle 430, and leaves vacuum and electric connection and Heat pipe joint.Space 450 between the inside and outside high vacuum seal cover 412,414 is imaging areas of hands and wrist.
In most of medical magnetic resonances were used, the operating frequency of radio-frequency coil was lower, from a few megahertz to one hundred megahertzes.In order to obtain so low resonant frequency, radio-frequency coil needs enough big inductance and electric capacity.Radio-frequency coil the most basic is to constitute by superconduction radio-frequency coil 510 and with it placed in-line resonant capacitance 515, shown in Fig. 5 A.
Superconduction radio-frequency coil and superconduction radio-frequency coil array are radiofrequency launchers, and it excites the part of patient body to make it to launch magnetic resonance signal.Another superconduction radio-frequency coil or superconduction radio-frequency coil array are as the magnetic resonance signal of receiving coil reception from patient.Superconduction radio-frequency coil and superconduction radio-frequency coil array are radiofrequency launchers in some designs, it excites the part of patient body to make it to launch magnetic resonance signal, and same superconduction radio-frequency coil or superconduction radio-frequency coil array are as the magnetic resonance signal of receiving coil reception from patient.
Radio-frequency coil can be by the superconduction band, the thick film superconductor, and thin film superconductor, or make as coppery non-superconducting metal.The superconduction radio-frequency coil has better signal to noise ratio under identical magnetic field.For example, the picture quality that the superconduction radio-frequency coil can provide the traditional copper radio-frequency coil could obtain under highfield more in the system of 3 teslas.Can save cost reaching under the prerequisite of same image resolution ratio the superconduction radiofrequency coil technology, because this technology can be selected the imaging system that has than downfield for use.For example, Di Jia 0.3 tesla's superconducting magnetic resonance coil can produce the picture quality that compares favourably with traditional 1 system of tesla.
In general the magnetostatic field direction that main magnet produces is parallel with the axis of vacuum insulation cover, is positioned at horizontal direction.The direction of the field that radiofrequency signal produces is vertical with the main field direction.Fig. 5 B, 5C, 5D, 5E, 5F have provided the example of the superconduction radio-frequency coil that satisfies these conditions.
Fig. 5 B is a saddle type radio-frequency coil, and it is made of superconduction inductance and placed in-line with it resonant capacitance 522.The superconduction radio-frequency coil is made of left coil 524 and right coil 526.The representative diameter of left coil 524 and right coil 526 is 1 to 20 centimetre.If the sense of current is clockwise directions at left coil 524, is counterclockwise 526 of right coils, and produces magnetic direction 528.Another kind of saddle type radio-frequency coil is shown in Fig. 5 C, inductance in the superconduction radio-frequency coil 530 and resonant capacitance 532 series connection, matching capacitance 534 links to each other superconduction radio-frequency coil 530 with terminal 536 in addition, thereby and ground wire 538 together with the radio signal transmission in the superconduction radio-frequency coil to the preamplifier of superconducting magnetic resonance imaging machine.Fig. 5 D has provided two preparations to be separated and adjacent on-chip superconduction radio-frequency coil 540,542.Each superconduction radio-frequency coil has a resonant capacitance 524 and matching capacitance 516.Another kind of situation is that the superconduction radio-frequency coil in the superconduction radio-frequency coil array is above two.In Fig. 5 E, each the saddle type superconduction radio-frequency coil 555 and the adjacent superconduction radio-frequency coil 555 of superconduction radio-frequency coil array 550 are overlapped.This method has been eliminated noise coupling between the superconduction radio-frequency coil has increased its imaging area simultaneously.In another example shown in Fig. 5 F, a quadrature superconduction radio-frequency coil 560 is made up of two saddle type superconduction radio-frequency coils 562,564, these two superconduction radio-frequency coils are the RF signal excitation of 90 degree by two phase contrasts, thereby improve the signal to noise ratio of radiofrequency signal.
The superconduction radio-frequency coil is to be made by the superconduction that is deposited on suitable substrate surface, and is installed on the low temperature heat-conducting plate.
Described superconduction radio-frequency coil can also be a multichannel array superconduction radio-frequency coil, and each passage has one and other coils not have the simple coils of coupling.
Except one vacuum insulation cover, the whole body superconducting magnetic resonance imaging machine that has can have two vacuum insulation covers, and imaging area is between two vacuum insulation covers, as shown in Figure 6A.This device 600 comprises a upper magnet 610 and lower magnet 612, last gradient coil 614, following gradient coil 616 and imaging area 640.Also have upper and lower vacuum insulation cover 620,630 in addition, each vacuum insulation cover all has fine vacuum interlayer and intermediary coarse vacuum district protecting superconduction radio-frequency coil 622,632 and corresponding low temperature heat-conducting plate 624,634.Superconduction radio-frequency coil 622,632 has good thermo-contact with low temperature heat-conducting plate 624,634 and links to each other with heat pipe 660,670 with 636 by heat integration 626.Heat pipe 660,670 links to each other with cryogenic system 190.Following vacuum insulation cover 630 is installed on the sick bed 650, thereby patient body is able near superconduction radio-frequency coil 632.Top superconduction radio-frequency coil 622 can be a transmitting coil, and following superconduction radio-frequency coil 632 is receiving coils.
Upper and lower gradient coil 614,616 is used to regulate main field between main magnet and imaging area.
Fig. 6 B has provided the example of the superconduction radio-frequency coil of another whole body imaging.The combination of low temperature heat-conducting plate is to be made of several low temperature heat-conducting plates 710 that are connected in the heat integration 712.Heat integration 712 is made by the good conductor of heat.Sapphire and aluminium oxide are the suitable materials of making low temperature heat-conducting plate 710 and heat integration 712.When main field strength was lower than 3 teslas, a spot of metal such as copper can be used to make low temperature heat-conducting plate 710 and heat integration 712.Low temperature heat-conducting plate 710 is to be made by narrow bonding jumper in such example, and it provides good conduction of heat and mechanical support can for superconduction radio-frequency coil 720, avoids the spiral electric current simultaneously.
System structure shown in Fig. 1,2 and 6 can change over multi-form imaging system, comprising foot, and knee, wrist, hands, neck, an imaging system.
Integrated superconducting magnetic resonance imaging machine described above depends on the heat pipe that connects low temperature heat-conducting plate and cryogenic system.In an example, heat pipe is made up of the heat conductor of strip and vacuum sleeve of being enclosed in around its.The coarse vacuum district of this vacuum sleeve and vacuum insulation cover links to each other.Another kind of situation is that vacuum sleeve is made up of the fine vacuum interlayer.One end of heat conductor links to each other with the low temperature heat-conducting plate, and the other end links to each other with heat exchanger 192.Heat pipe effectively reaches heat exchanger 192 with heat from the low temperature heat-conducting plate.In an example, heat conductor is the strip shell formation by the mixed body that cryogenic fluid and steam thereof are housed (as liquid helium, liquid nitrogen and their steam).The hot junction of heat pipe or low temperature heat-conducting plate end will be lower than its cold junction or heat exchanger end, as shown in Figure 1.Steam is cooled and converts liquid at the heat exchanger end, and the low side that liquid flows to heat pipe arrives the low temperature heat-conducting plate, there Liquid Absorption heat and being evaporated.Thereby steam flows to heat pipe high-endly passes to heat exchanger to heat and is transformed into liquid, finishes a heat cycle.Heat pipe can be a solid bar-shaped Heat Conduction Material in another case, and this Heat Conduction Material comprises copper, sapphire, and ceramic rod, or copper strips, and surround by vacuum sleeve.The hot junction of heat pipe also can be higher than or etc. be higher than its cold junction.The porous network structure of inside heat pipe can apply a capillary pressure on the working medium of liquid phase in this case.This porous network structure material is fired by metal dust and is formed or be made up of the groove that is parallel to the heat pipe axis.
In other cases, refrigeration machine can be selected the Gifford-McMahhon refrigeration machine for use, TJ refrigeration machine, sterlin refrigerator.
More than by specific embodiment the present invention is had been described in detail, but these are not to be construed as limiting the invention.Be appreciated that above-mentioned general description all is the indivedual examples of quoting in order further to explain the present invention that are easy to explain.Under the situation that does not break away from the principle of the invention, those skilled in the art also can make many distortion and improvement, and these also should be considered as belonging to protection scope of the present invention.
Claims (30)
1. superconducting magnetic resonance imaging machine comprises: imaging area, and at least one vacuum insulation cover, one produces the main magnet in magnetic field at imaging area, it is characterized in that: also comprise a cryogenic system that links to each other with the vacuum insulation cover;
Described vacuum insulation cover is a double-layer seal fine vacuum interlayer, and the vacuum in its interlayer is 10
-6To 10
-12Between the holder, the vacuum insulation cover surrounds a vacuum 10
-3To 10
-6Coarse vacuum district between the holder;
At least one superconduction radio-frequency coil is installed in the coarse vacuum district, and this superconduction radio-frequency coil provides a described imaging area at vacuum insulation cover near surface;
Low temperature heat-conducting plate in superconduction radio-frequency coil and the coarse vacuum district keeps thermo-contact; The low temperature heat-conducting plate links to each other to keep the superconduction radio-frequency coil to be in required low temperature state by a heat pipe with cryogenic system.
2. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: also comprise a patient support, described vacuum insulation cover is installed in this support.
3. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described coarse vacuum district links to each other with vacuum tube, and with O type circle, vacuum packing ring, or epoxy sealing.
4. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described double-layer seal fine vacuum interlayer is to use G10 fiberglass, glass and quartz, and perhaps their combination is made.
5. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: the thickness of described double-layer seal fine vacuum interlayer is between 1 millimeter to 100 millimeters.
6. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: also comprise the low temperature cold head that links to each other with the low temperature heat-conducting plate, this low temperature cold head links to each other with cryogenic system to fetch by heat pipe and keeps the required low temperature of superconduction radio-frequency coil.
7. superconducting magnetic resonance imaging machine as claimed in claim 6 is characterized in that: described low temperature cold head is made by copper billet.
8. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described low temperature heat-conducting plate is made by at least one block of nonmagnetic substance, and described nonmagnetic substance is a pottery, plastics, crystal, metal, glass and quartz.
9. superconducting magnetic resonance imaging machine as claimed in claim 8 is characterized in that: described crystal is a sapphire.
10. superconducting magnetic resonance imaging machine as claimed in claim 8 is characterized in that: described pottery is an aluminium oxide.
11. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described heat pipe is made up of the heat conductor of strip and vacuum sleeve of being enclosed in around its, and this heat conductor is made of the strip shell of the mixed body that cryogenic fluid and steam thereof are housed.
12. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described heat pipe is a bar-shaped Heat Conduction Material, and this Heat Conduction Material comprises copper, crystal, and pottery, or copper strips, and surround by vacuum sleeve.
13. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described cryogenic system comprises a heat exchanger, a refrigeration machine and a compressor.
14. superconducting magnetic resonance imaging machine as claimed in claim 13 is characterized in that: described refrigeration machine is a vascular refrigerator, GM refrigeration machine, TJ refrigeration machine, and sterlin refrigerator.
15. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is made by high-temperature superconducting thin film.
16. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is to be made by hts band or line.
17. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is equipped with at least a superconductor, and this superconductor is YBaCuO, BiSrCaCuO, TlBiCaCuO and boronation magnesium compound.
18. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is a radiofrequency launcher, excites the part of patient body to produce magnetic resonance signal.
19. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil receives from the intravital magnetic resonance signal of patient as receiving coil.
20. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is as transmitting coil and receiving coil, launches and accepts magnetic resonance signal.
21. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: also comprise at least one gradient coil, it is used to regulate main field between main magnet and imaging area.
22. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is for containing the coil by superconductor preparation of a diameter between 10 to 200 millimeters at least.
23. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is at least one crossed coil or coil array.
24. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described superconduction radio-frequency coil is a multichannel array coil, and each passage has one and other coils not have the simple coils of coupling.
25. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described vacuum insulation cover is two, and described imaging area is between two vacuum insulation covers.
26. superconducting magnetic resonance imaging machine as claimed in claim 2 is characterized in that: described patient support is a removable sick bed.
27. superconducting magnetic resonance imaging machine as claimed in claim 26 is characterized in that: described cryogenic system has at least a part to be installed in the removable sick bed.
28. superconducting magnetic resonance imaging machine as claimed in claim 1 is characterized in that: described vacuum insulation cover and cryogenic system are by stent support.
29. the arbitrary described superconducting magnetic resonance imaging machine of claim 1-28 is at whole body, knee, wrist, hands, foot, the application in a neck and the imaging.
30. a method of making superconducting magnetic resonance imaging machine is characterized in that, comprising: an imaging area is provided, a patient support system, at least one vacuum insulation cover, a main magnet and a refrigeration system that is installed in the patient support system that is used for producing main field at imaging area;
Build a vacuum pressure between 10
-6To 10
-12Double-layer seal fine vacuum interlayer between the holder; Surround a vacuum pressure between 10 with double-layer seal fine vacuum interlayer
-6To 10
-12Coarse vacuum district between the holder;
A superconduction radio-frequency coil is installed in the coarse vacuum district at least and it is linked to each other with the low temperature heat-conducting plate; The low temperature heat-conducting plate is linked to each other to keep the required low temperature of superconduction radio-frequency coil by a heat pipe with cryogenic system.
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| CN102680924A (en) * | 2012-05-22 | 2012-09-19 | 江苏美时医疗技术有限公司 | High-temperature superconducting surface radio-frequency receiving coil for magnetic resonance imaging and operation method thereof |
| CN103116147A (en) * | 2013-02-26 | 2013-05-22 | 江苏美时医疗技术有限公司 | Knee radiofrequency coil for magnetic resonance imaging system |
| CN104337515A (en) * | 2013-07-23 | 2015-02-11 | 西门子公司 | Local Coil for a Coil System of a Magnetic Resonance Imaging System |
| CN107732457A (en) * | 2017-09-30 | 2018-02-23 | 苏州美柯医疗科技有限公司 | antenna element and array antenna |
| CN116559743A (en) * | 2023-06-13 | 2023-08-08 | 中国科学院深圳先进技术研究院 | Radio frequency signal receiving system for magnetic resonance imaging |
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| CN102680923A (en) * | 2012-05-22 | 2012-09-19 | 江苏美时医疗技术有限公司 | High-temperature superconductivity knee joint radio frequency receiving coil device used for magnetic resonance imaging |
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| JP2005310811A (en) * | 2004-04-16 | 2005-11-04 | Hitachi Ltd | Superconductive magnet device |
| JP4908960B2 (en) * | 2006-07-27 | 2012-04-04 | 株式会社日立製作所 | Superconducting magnet apparatus and magnetic resonance imaging apparatus |
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| CN102680924A (en) * | 2012-05-22 | 2012-09-19 | 江苏美时医疗技术有限公司 | High-temperature superconducting surface radio-frequency receiving coil for magnetic resonance imaging and operation method thereof |
| CN103116147A (en) * | 2013-02-26 | 2013-05-22 | 江苏美时医疗技术有限公司 | Knee radiofrequency coil for magnetic resonance imaging system |
| CN103116147B (en) * | 2013-02-26 | 2015-11-25 | 江苏美时医疗技术有限公司 | A kind of knee radiofrequency coil for magnetic resonance imaging system |
| CN104337515A (en) * | 2013-07-23 | 2015-02-11 | 西门子公司 | Local Coil for a Coil System of a Magnetic Resonance Imaging System |
| CN107732457A (en) * | 2017-09-30 | 2018-02-23 | 苏州美柯医疗科技有限公司 | antenna element and array antenna |
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| CN116559743A (en) * | 2023-06-13 | 2023-08-08 | 中国科学院深圳先进技术研究院 | Radio frequency signal receiving system for magnetic resonance imaging |
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