CN203149101U - Head radio frequency coil for magnetic resonance imaging system - Google Patents
Head radio frequency coil for magnetic resonance imaging system Download PDFInfo
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- CN203149101U CN203149101U CN 201320086750 CN201320086750U CN203149101U CN 203149101 U CN203149101 U CN 203149101U CN 201320086750 CN201320086750 CN 201320086750 CN 201320086750 U CN201320086750 U CN 201320086750U CN 203149101 U CN203149101 U CN 203149101U
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Abstract
The utility model discloses a head radio frequency coil for a magnetic resonance imaging system, comprising a coil housing (1), a vacuum cap (2), a liquid nitrogen device and a coil conductor (3). The radio frequency coil comprises at least one radio frequency receiving coil or at least one maneuverable radio frequency coil which can be used for emission and reception; the coil conductor (3) comprises an end ring (4), an even number of parallel legs (5) which connect two ends of the end ring and a resonant capacitor (6); the resonant capacitor (6) is connected with the coil conductor (3); the coil conductor (3) with a different structure is selected according to different direction of a main magnetic field; the liquid nitrogen device is arranged on the coil conductor (3), and the coil conductor is cooled by liquid nitrogen; the coil conductor can be applied as a receiving coil and a reception/transmitting coil; good quadrature reception and excitation performance is provided, the uniformity in an imaging area is high, the conductor is cooled by liquid nitrogen, the loss in the magnetic resonance reception process is reduced, the thermal noise generated by resistance is decreased, and thereby the signal to noise ratio of an obtained image is raised.
Description
Technical field
The utility model relates to a kind of head radio-frequency coil for magnetic resonance imaging system, refers more particularly to a kind of radio-frequency coil that adopts liquid nitrogen refrigerating and with the coil-conductor with reception or transmitting/receiving head is diagnosed.
Background technology
At present, mr imaging technique has been widely used in the world each large-scale medical institutions and has obtained huge and unique benefit in medical practice.These mr imaging techniques not only have at identification and assessment pathology, judge that the medical diagnosis aspect the tested tissue health situation is worth, also be widely used in clinical and research in; Though by unremitting effort, magnetic resonance imaging has obtained significant progress, magnetic resonance imaging also has the needs that further improve, as the signal to noise ratio (S/N ratio) of higher contrast, enhancing, picking rate and/or higher room and time resolution faster.
Coil is the core component of picking up magnetic resonance signals, the ability size of coil pickoff signals and the height of quality, image quality is had direct fundamental influence, and in the magnetic resonance imaging system, the magnetic resonance signal that sends after proton is stimulated in the human body is very faint.An important index of coil is quality factor, generally be abbreviated as Q, it is got divided by the width of harmonic peak by the centre frequency of the harmonic peak of coil, what its reflected is that coil receives signal and gets rid of interference capability, under the prerequisite of coil available bandwidth greater than the required bandwidth of magnetic resonance system, unloaded Q is normally more high more good.The principal element that determines the Q of coil is the resistance in the whole winding loop, mainly is the resistance in the conductor, and conductor resistance is more big, and the Q of coil is also just more low, and image quality is more poor.
The existing method that adopts is: reduce coil overlapping part coupling capacitance by improving wiring, thereby improve the Q value of coil, but because being subject to intrinsic resistance in the normal temperature copper conductor, the Q value is still not high enough, the pattern noise related with the electronics thermonoise influences imaging definition, the conductor that uses is the normal temperature copper conductor, in the imaging process, in order to weaken the influence that brings with electronics thermonoise and intrinsic resistance in the copper conductor, must improve signal to noise ratio (S/N ratio) by prolonging sweep time, thereby cause the raising of equipment use cost; Coil design commonly used at present generally all can not obtain higher unloaded Q mainly based on the normal temperature conductor.
Summary of the invention
The technical problems to be solved in the utility model provides a kind of head radio-frequency coil for magnetic resonance imaging system, this coil and all kinds of magnetic resonance system are used, be mainly used in each position of head and comprise the clinical scanning at brain, cerebellum, brain stem, sinus frontalis, maxillary sinus position, the paramedical personnel diagnoses.
In order to solve the problems of the technologies described above, the utility model provides a kind of head radio-frequency coil for magnetic resonance imaging system, this radio-frequency coil comprises coil case, vacuum (-tight) housing, liquid nitrogen plan, coil-conductor and low-noise preamplifier, this radio-frequency coil both can be launched also receivable radio-frequency coil at least one RF receiving coil or at least one operability, described coil-conductor is by end ring, the even number leg parallel to each other that connects the end ring two ends becomes with the resonance capacitance group, described resonant capacitance links to each other with coil-conductor, can be according to the coil-conductor of the different choice different structure of main field direction, described coil-conductor adopts high pass, the logical three kinds of structures of low pass and band are judged the coil-conductor structure according to resonant capacitance diverse location in coil-conductor; Described liquid nitrogen plan comprises liquid nitrogen container and liquid nitrogen filler pipe, and described liquid nitrogen plan is arranged on the coil-conductor and by liquid nitrogen coil-conductor is freezed, and the signal output part of described coil-conductor links to each other with low-noise preamplifier.
Described coil-conductor adopts electric conductivity a kind of non-superconducting material and the superconductor higher than copper when being cooled to the 0K-77K temperature, and described coil-conductor adopts high temperature superconducting materia.
Described vacuum (-tight) housing is provided with to be taken out mouthful and is connected with vaccum-pumping equipment, it is indoor that described coil-conductor is placed on a common vacuum that is isolated by the non magnetic nonmetal liquid nitrogen container that constitutes and vacuum (-tight) housing, described common vacuum is indoor to be provided with non magnetic nonmetallic insulation material, and described insulation material is pearlife or aerogel blanket.
Described liquid nitrogen filler pipe passes vacuum (-tight) housing and is connection status with liquid nitrogen container, and described liquid nitrogen container is arranged at vacuum (-tight) housing inside by non magnetic nonmetallic materials, and described coil-conductor is cylindric, and described coil-conductor is provided with a perforate as the scan test section territory.
As further improvement of the utility model, it is inner or outside that described coil-conductor partly or entirely is arranged on liquid nitrogen container, and coil-conductor partly or entirely contacts with the liquid nitrogen container outside surface by non magnetic electrical isolation low temperature conductive material.
Compared with prior art, the utlity model has following advantage.
(1) coil-conductor that relates in the utility model adopts electric conductivity a kind of non-superconducting material and the superconductor higher than copper when being cooled to the 0K-77K temperature, described coil-conductor adopts high temperature superconducting materia, coil-conductor can use as receiving coil, also can use as reception/transmitting coil, the electromagnetic field height that produces is even, and coil has high symmetry, realize that easily quadrature transmits and receives, having preferably, quadrature receives and excitating performance, during the quadrature emission, it is low in energy consumption, when quadrature receives, and the coil height of the more nonopiate reception of signal to noise ratio (S/N ratio).
(2) described coil-conductor adopts the logical three kinds of structures of high pass, low pass and band, the resonant capacitance of high-pass type birdcage coil all is welded on the end ring conductor, the resonant capacitance of low pass type is welded in the middle of the every leg conductor, the logical molded lines circle of band then all is furnished with electric capacity on end ring and leg, can select dissimilar coil-conductors according to different main field directions.
(3) pass through the coil-conductor liquid nitrogen refrigerating, reduce the resistance of conductor, the use normal conductor at low temperatures, the resistance meeting is obvious reduces, and when using the super material of high temperature that can under liquid nitrogen temperature, work as conductor, resistance can be reduced to the degree of ignoring, thereby significantly improves the Q of coil; Electronics thermonoise in the conductor is proportional to the product of temperature and resistance, and when temperature was reduced to liquid nitrogen temperature from room temperature, the electronics thermonoise in the coil-conductor can significantly reduce.
By to conductor with liquid nitrogen refrigerating reduce in the magnetic resonance receiving course loss and because the thermonoise that resistance produces, thereby improve the signal to noise ratio (S/N ratio) that obtains image, obviously the signal receiving performance of intensifier coil significantly improves the picture quality of magnetic resonance imaging.
(4) described vacuum (-tight) housing is provided with and takes out mouthful and be connected with vaccum-pumping equipment, it is indoor that described coil-conductor is placed on a common vacuum that is isolated by the non magnetic nonmetal liquid nitrogen container that constitutes and vacuum (-tight) housing, so just, liquid nitrogen container and extraneous room temperature can be kept apart, just can keep low temperature for a long time.Described common vacuum is indoor to be provided with non magnetic nonmetallic insulation material, and described insulation material is pearlife or aerogel blanket, with further raising heat insulation effect.
(5) described liquid nitrogen container is arranged at vacuum (-tight) housing inside by non magnetic nonmetallic materials, prevents that liquid nitrogen container from relatively moving, and liquid nitrogen container does not contact with vacuum (-tight) housing, in the hope of reduce cold consumption as far as possible.
(6) described coil is cylindric, described coil is provided with a perforate as the scan test section territory, middle perforate can allow the patient's that lays flat on one's back head put into wherein, consider that the part patient suffers from claustrophobia, the position of the corresponding eyes of hollow cylinder can also perforate, so just can not shelter from patient's the visual field fully.
Description of drawings
Figure 1A is used for the structural representation of the head radio-frequency coil of magnetic resonance imaging system for the utility model.
Figure 1B is used for the cross sectional representation of the head radio-frequency coil of magnetic resonance imaging system for the utility model.
Fig. 2 A is schematic diagram when coil-conductor is receiving mode in the utility model.
Fig. 2 B is schematic diagram when coil-conductor is for conduct reception/transmitting coil pattern in the utility model.
Fig. 3 A is the high-pass structure synoptic diagram of coil-conductor in the utility model.
Fig. 3 B is the lowpass structures synoptic diagram of coil-conductor in the utility model.
Fig. 3 C is a kind of application synoptic diagram of coil-conductor in the utility model
Embodiment
Embodiment one.
Shown in Figure 1A, Figure 1B and Fig. 2 A, a kind of head radio-frequency coil for magnetic resonance imaging system, this radio-frequency coil comprises coil case 1, vacuum (-tight) housing 2, liquid nitrogen plan, coil-conductor 3 and low-noise preamplifier 7, this radio-frequency coil is a RF receiving coil, be in receiving mode during work, need another by the transmitting coil that the MRI system carries tested article to be excited, receive the signal that tested article produce by receiving coil then.
As Fig. 3 A, shown in Fig. 3 B and Fig. 3 C, described coil-conductor 3 is by end ring 4, the even number leg 5 parallel to each other and the resonant capacitance 6 that connect the end ring two ends are formed, can weld resonant capacitance 6 to reach condition of resonance on end ring 4 or the individual leg 5, there is different voltage differences at resonant capacitance 6 two ends of diverse location, can be on selected one or more resonant capacitances two ends overlap joint the matching network system voltage difference at these electric capacity two ends is converted into the available signal of system, described coil-conductor 3 adopts high pass, the logical three kinds of structures of low pass and band, the resonant capacitance 6 of high-pass type coil all is welded on the end ring conductor, the resonant capacitance of low pass molded lines circle is welded on the centre of every leg conductor, the resonant capacitance 6 of the logical molded lines circle of band all is provided with on end ring 4 and a leg 5, can select dissimilar coil-conductor structures according to resonant capacitance diverse location in coil-conductor.
Described liquid nitrogen plan comprises liquid nitrogen container 8 and liquid nitrogen filler pipe 9, described liquid nitrogen plan is arranged on the coil-conductor 3, it is inner or outside that described coil-conductor 3 partly or entirely is arranged on liquid nitrogen container 8, that is: coil-conductor 3 has following several from the method that liquid nitrogen container 8 obtains refrigeration:
(i) coil-conductor 3 partly or entirely is placed in the liquid nitrogen container 8, and coil-conductor 3 directly is immersed in the liquid nitrogen and cooled, and remainder stretches out liquid nitrogen container 8, and is cooled by the thermal conduction capability of conductor self;
(ii) the coil-conductor 3 part or all of outside surfaces that directly are bonded at liquid nitrogen container with glue are and cooled, and remainder is cooled by the thermal conduction capability of conductor self;
(iii) coil-conductor 3 partly or entirely contacts with liquid nitrogen container 8 outside surfaces through non magnetic electrical isolation low temperature conductive material (for example sapphire, aluminium nitride) and cooled, and remainder passes through the thermal conduction capability of conductor self and cooled;
(ⅳ) combination of above three kinds of modes.
Described liquid nitrogen filler pipe 9 passes vacuum (-tight) housing 2 and is connection status with liquid nitrogen container 8, described liquid nitrogen container 8 is arranged at vacuum (-tight) housing 2 inside by non magnetic nonmetallic materials, that is: liquid nitrogen container 8 tops are stretched out one or two liquid nitrogen filler pipes 9 and are passed vacuum (-tight) housing 2, being convenient to the external world adds liquid nitrogen and allows the inside nitrogen discharged to the external world to liquid nitrogen container 8 the insides, can also with non magnetic nonmetallic materials liquid nitrogen container 8 be supported and fixed on the correct position of vacuum (-tight) housing 2 the insides at suitable position, prevent that liquid nitrogen container 8 from relatively moving, except liquid nitrogen filler pipe 9 and a spot of strong point, liquid nitrogen container 8 does not contact with vacuum (-tight) housing 2, in the hope of reduce cold consumption as far as possible.
Described coil-conductor 3 adopts electric conductivity a kind of non-superconducting material and the superconductor higher than copper when being cooled to the 0K-77K temperature, the various temperature combination is arranged for keeping the coil running.For example, under some configuration mode, all coils may all maintain 77K; Described coil-conductor 3 adopts high temperature superconducting materias, as YBaCuO, BiSrCaCuO etc., also can adopt superconductor, nano material such as carbon nano-tube and have the material of high conductivity characteristics.
Described vacuum (-tight) housing 2 is provided with takes out mouthfuls 10 and be connected with vaccum-pumping equipment, described coil-conductor 3 is placed on by non magnetic nonmetal (epoxy resin fiberglass for example, double thermal insulation glass) common vacuum isolating of the liquid nitrogen container 8 of Gou Chenging and vacuum (-tight) housing 2 is indoor, described common vacuum is indoor to be provided with non magnetic nonmetallic insulation material, and described insulation material is pearlife or aerogel blanket.
The signal output part of described coil-conductor 3 links to each other with low-noise preamplifier 7, and the signal of sensing during coil working is delivered to system signal processing rear end by a low loss cable and handled after low-noise preamplifier 7 amplifies.Prime amplifier 7 can be operated under the room temperature environment, also can contact with refrigerant, is operated in liquid nitrogen temperature.
Described coil-conductor 3 is cylindric, and described coil-conductor 3 is provided with a perforate as the scan test section territory.Liquid nitrogen container 8 and vacuum (-tight) housing 2 are hollow cylinder, middle perforate can allow the patient's that lays flat on one's back head put into wherein, consider that the part patient suffers from claustrophobia, the position of the corresponding eyes of hollow cylinder can also perforate, so just can not shelter from patient's the visual field fully.
Be assembled into line operate according to said structure, at first taking out on external vacuum extractor and the vacuum (-tight) housing 2 mouthfuls 10 is connected and vacuumizes, make to reach certain vacuum tightness in the space between vacuum (-tight) housing 2 and the liquid nitrogen container 8, good seal is taken out mouthful 10 disconnection vacuum pumps then, installs shell 1.
By 9 pairs of liquid nitrogen containers of liquid nitrogen filler pipe, 8 filling liquid nitrogen, make the coil 3 that is in contact with it cool to liquid nitrogen temperature again, the temperature of liquid nitrogen container 8 can drop to 77K.
Whole refrigeration is placed into the main field center of magnetic resonance system, and the output line of coil and system signal are handled the rear end be connected, patient's head is placed in the hub of a spool perforate, the transmitting coil that is carried by the MRI system excites tested article, receive the signal that tested article produce by receiving coil then, the signal of sensing during coil working is delivered to system signal processing rear end by a low loss cable and is handled scanning and imaging after low-noise preamplifier 7 amplifies.
Embodiment two.
Shown in Figure 1A, Figure 1B and Fig. 2 B, a kind of head radio-frequency coil for magnetic resonance imaging system, this radio-frequency coil comprises coil case 1, vacuum (-tight) housing 2, liquid nitrogen plan, coil-conductor 3 and low-noise preamplifier 7, during as reception/transmitting coil, exciting with receiving coil is same coil.
At first taking out on external vacuum extractor and the vacuum (-tight) housing 2 mouthfuls 10 is connected and vacuumizes, make to reach certain vacuum tightness in the space between vacuum (-tight) housing 2 and the liquid nitrogen container 8, good seal is taken out mouth 10 disconnection vacuum pumps then, installs shell 1.
By 9 pairs of liquid nitrogen containers of liquid nitrogen filler pipe, 8 filling liquid nitrogen, make the coil 3 that is in contact with it cool to liquid nitrogen temperature again, the temperature of liquid nitrogen container 8 can drop to 77K.
Whole refrigeration is placed into the main field center of magnetic resonance system, and the output line of coil is handled the rear end with system signal is connected, patient's head is placed in the hub of a spool perforate, at first, coil working sends energy in emission mode, and tested article are excited; After finishing, coil working no longer sends energy in receiving mode, and only receive the signal that tested article produce, the signal of sensing during coil working is delivered to system signal processing rear end by a low loss cable and is handled scanning and imaging after low-noise preamplifier 7 amplifies.
Claims (10)
1. head radio-frequency coil that is used for magnetic resonance imaging system, this radio-frequency coil comprises coil case (1), vacuum (-tight) housing (2), liquid nitrogen plan, coil-conductor (3) and low-noise preamplifier (7), it is characterized in that: this radio-frequency coil both can be launched also receivable radio-frequency coil at least one RF receiving coil or at least one operability, described coil-conductor (3) is by end ring (4), the even number leg (5) parallel to each other and the resonant capacitance (6) that connect the end ring two ends are formed, described resonant capacitance (6) links to each other with coil-conductor (3), can be according to the coil-conductor (3) of the different choice different structure of main field direction, described liquid nitrogen plan is arranged at coil-conductor (3) and upward and by liquid nitrogen coil-conductor is freezed, and the signal output part of described coil-conductor (3) links to each other with low-noise preamplifier (7).
2. the head radio-frequency coil for magnetic resonance imaging system according to claim 1, it is characterized in that: described coil-conductor (3) adopts the logical three kinds of structures of high pass, low pass and band, judges coil-conductor (3) structure according to resonant capacitance (6) diverse location in coil-conductor (3).
3. the head radio-frequency coil for magnetic resonance imaging system according to claim 1, it is characterized in that: described liquid nitrogen plan comprises liquid nitrogen container (8) and liquid nitrogen filler pipe (9).
4. the head radio-frequency coil for magnetic resonance imaging system according to claim 1 is characterized in that: electric conductivity a kind of non-superconducting material and the superconductor higher than copper when described coil-conductor (3) employing is cooled to the 0K-77K temperature.
5. the head radio-frequency coil for magnetic resonance imaging system according to claim 4 is characterized in that: described coil-conductor (3) employing high temperature superconducting materia.
6. the head radio-frequency coil for magnetic resonance imaging system according to claim 1, it is characterized in that: described vacuum (-tight) housing (2) is provided with to be taken out mouthful (10) and is connected with vaccum-pumping equipment, and it is indoor that described coil-conductor (3) is placed on a common vacuum that is isolated by the non magnetic nonmetal liquid nitrogen container that constitutes (8) and vacuum (-tight) housing (2).
7. the head radio-frequency coil for magnetic resonance imaging system according to claim 1, it is characterized in that: it is inner or outside that described coil-conductor (3) partly or entirely is arranged on liquid nitrogen container (8), and coil-conductor (3) partly or entirely contacts with the liquid nitrogen container outside surface by non magnetic electrical isolation low temperature conductive material.
8. the head radio-frequency coil for magnetic resonance imaging system according to claim 6 is characterized in that: described common vacuum is indoor to be provided with non magnetic nonmetallic insulation material, and described insulation material is pearlife or aerogel blanket.
9. according to claim 1 or 3 described head radio-frequency coils for magnetic resonance imaging system, it is characterized in that: described liquid nitrogen filler pipe (9) passes vacuum (-tight) housing (2) and is connection status with liquid nitrogen container (8), and described liquid nitrogen container (8) is arranged at vacuum (-tight) housing (2) inside by non magnetic nonmetallic materials.
10. the head radio-frequency coil for magnetic resonance imaging system according to claim 1 is characterized in that: described coil-conductor (3) is for cylindric, and described coil-conductor (3) is provided with a perforate as the scan test section territory.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 201320086750 CN203149101U (en) | 2013-02-26 | 2013-02-26 | Head radio frequency coil for magnetic resonance imaging system |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 201320086750 CN203149101U (en) | 2013-02-26 | 2013-02-26 | Head radio frequency coil for magnetic resonance imaging system |
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| CN203149101U true CN203149101U (en) | 2013-08-21 |
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| CN 201320086750 Expired - Lifetime CN203149101U (en) | 2013-02-26 | 2013-02-26 | Head radio frequency coil for magnetic resonance imaging system |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103116146A (en) * | 2013-02-26 | 2013-05-22 | 江苏美时医疗技术有限公司 | Head radiofrequency coil for magnetic resonance imaging system |
-
2013
- 2013-02-26 CN CN 201320086750 patent/CN203149101U/en not_active Expired - Lifetime
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103116146A (en) * | 2013-02-26 | 2013-05-22 | 江苏美时医疗技术有限公司 | Head radiofrequency coil for magnetic resonance imaging system |
| CN103116146B (en) * | 2013-02-26 | 2015-11-25 | 江苏美时医疗技术有限公司 | A kind of head radiofrequency coil for magnetic resonance imaging system |
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Effective date of registration: 20160726 Granted publication date: 20130821 |
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| PD01 | Discharge of preservation of patent |
Date of cancellation: 20170726 Granted publication date: 20130821 |
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| CX01 | Expiry of patent term |
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