CN204410816U - A kind of nuclear magnetic resonance imaging instrument device - Google Patents
A kind of nuclear magnetic resonance imaging instrument device Download PDFInfo
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- CN204410816U CN204410816U CN201420860376.5U CN201420860376U CN204410816U CN 204410816 U CN204410816 U CN 204410816U CN 201420860376 U CN201420860376 U CN 201420860376U CN 204410816 U CN204410816 U CN 204410816U
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- coil
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- gradient coil
- main magnet
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Abstract
The utility model discloses a kind of nuclear magnetic resonance imaging instrument device, comprise imaging region, main magnet, gradient coil, radio-frequency coil, sick bed, the independent main magnet arranged, be connected to gradient coil and radio-frequency coil, the central authorities of described main magnet are provided with the space stretched into for described sick bed, gradient coil and radio-frequency coil.Described instrument meets the needs of current electronic product to high frequency, big current, miniaturization, energy-saving future development, and reduce further corresponding cost and maintenance cost.
Description
Technical field
This utility model relates to a kind of nuclear magnetic resonance imaging instrument device with independent main magnet structure.
Background technology
Nuclear magnetic resonance (MRI, English full name: magnetic resonance imaging) instrument is often used to medicine and hygiene fields, namely hydrogen nuclei in tissue (proton) is utilized in magnetic field, to be subject to the excitation of radio-frequency pulse and nmr phenomena occurs, produce magnetic resonance signal, through electronic computer process, reconstruct the imaging technique of the image of a certain aspect of human body.
In nuclear magnetic resonance application, as shown in Figure 1, patient body 1 (or object) is placed in an imaging region 2, and imaging region 2 is determined by the design of nuclear magnetic resonance imaging instrument device parts and location layout.The integrated instrument structure of existing routine contains fixing successively from outside to inside main magnet 3, gradient coil 4 and radio-frequency coil 5, one of them problem is that the central space for placing patient body 1 is very limited, owing to being also placed with sick bed 6 simultaneously, the patient therefore lain down easily produces closed fear.In order to position to be imaged for patient body 1 is placed in imaging region 2 rightly, some limbs imagings, as shoulder, can be very difficult, the patient large for build or even impossible.
Therefore, how to provide a kind of central space placing patient body comparatively large, and imaging region more flexibly nuclear magnetic resonance imaging instrument device be those skilled in the art's technical problem urgently to be resolved hurrily.
Utility model content
This utility model provides a kind of nuclear magnetic resonance imaging instrument device, to expand the central space placing patient body, and improves the motility of imaging region.
For solving the problems of the technologies described above, this utility model provides a kind of nuclear magnetic resonance imaging instrument device, a kind of nuclear magnetic resonance imaging instrument device, it is characterized in that, comprise imaging region 20, main magnet 30, gradient coil 40, radio-frequency coil 50, sick bed 60, the independent main magnet 30 arranged, is connected to gradient coil 40 and radio-frequency coil 50, and the central authorities of described main magnet 30 are provided with the space stretched into for described sick bed 60, gradient coil 40 and radio-frequency coil 50; Wherein said main magnet 30 comprises column 1a, upper and lower housing cap 2a, semicircle magnet steel 3a, semicircle pole plate 4a, semicircle eddy-current disc 5a, semicircle grading ring 6a, gradient coil 7a, transmitting coil 8a, imaging area 9a; Described upper and lower housing cap 2a and column 1a is bolted composition building block assembling C type yoke; On described upper and lower housing cap 2a, symmetry is equipped with magnet steel 3a, pole plate 4a, grading ring 6a, eddy-current disc 5a, gradient coil 7a and transmitting coil 8a in order, is the formation imaging area, hemisphere territory of 600mm in permanent magnet center zone diameter; On described pole plate, grading ring is equipped with in outer end; Described grading ring is built with eddy-current disc; Gradient coil and transmitting coil be also equipped with in described grading ring, eddy-current disc.
Preferably, also comprise shimming parts, described shimming parts are connected on described sick bed.
Preferably, described gradient coil, radio-frequency coil and shimming parts or packaged type detachable with described sick bed is connected.
Preferably, the size of described gradient coil, radio-frequency coil and shimming parts is corresponding with each body part of patient with position.
Outside the Pass the generation of eddy current and magnetization condition, eddy-current disc physical dimension have, also relevant with the resistivity of eddy-current disc material (being inversely proportional to), the eddy current that pole plate produces can be eliminated or reduce to the eddy-current disc adopting the high Fe-based amorphous alloy soft magnetism band 1K 101 of resistivity of material to make better, signal to noise ratio is more excellent, and imaging is more clear; Amorphous is a kind of novel magnetically soft alloy material, it adopts super chilling technique directly to be cooled with the speed of 1,000,000 degree per second by motlten metal, form the noncrystal strip that thickness is 25--28 μm, obtain that atomic arrangement combination has shortrange order, the non-crystaline amorphous metal tissue of longrange disorder feature, microstructure is different from traditional metal and alloy material completely.Fe-based amorphous band has ultramicro crystal kernel structure, with its high pcrmeability, high saturated magnetic strength, low iron loss and excellent stability, meet the needs of current electronic product to high frequency, big current, miniaturization, energy-saving future development, silicon steel and ferrite can be substituted, be applied in the permanent magnet of nuclear magnetic resonance imaging instrument.
Adopt primarily of Pr/Nd=0.2 ~ 0.4, Pr
25nd
75n52 ~ N55 high-performance Ne-Fe-B of 29 ~ 31wt%, Co 0.9 ~ 1.5wt%, Cu0.1 ~ 0.3wt% composition reduces the use of heavy rare earth dysprosium, thus reduces production cost; In magnet steel, CoCu's combines to add and not only increases corrosion resistance and improve again magnet steel magnetic property.Adopt gradient, launch integrated coil and can realize permanent magnet height dimension and reduce, be bolted composition building block assembling C type yoke, can realize overall mass and alleviate, processing technique is simple, and structure is changeable and be convenient to shimming.
Compared to prior art, the nuclear magnetic resonance imaging instrument utensil that this utility model provides has the following advantages:
1. this utility model structure replacing main magnet, gradient coil and radio-frequency coil integral molding independent of the described gradient coil of main magnet and the separate type of radio-frequency coil, described main magnet provides more how utilizable space for patient and radiologist, it can make the patient of closed phobia be loosened, can also open up new clinical practice, such as NMR (Nuclear Magnetic Resonance)-imaging is for the application needed in the body kinematics imaging in more spaces;
2. while provide an equal size imaging region for patient, this utility model can reduce main magnet size and reduce 5 gaussian lines significantly, thus reduces cost and the shielding space cost of Magnet further;
3. in High-Field situation, this utility model uses relatively little main magnet, alleviates worry that weight increases and reduces the consumption when more high magnetic field intensity for cold-producing medium.
Accompanying drawing explanation
Fig. 1 is the structural representation of the nuclear magnetic resonance imaging instrument device of prior art;
Fig. 2 is the structural representation (head imaging) of the nuclear magnetic resonance imaging instrument device of this utility model one detailed description of the invention;
Fig. 3 is the structural representation (foot's imaging) of the nuclear magnetic resonance imaging instrument device of this utility model one detailed description of the invention.
Fig. 4 is C type magnet structure schematic diagram
In Fig. 1: 1-patient body, 2-imaging region, the main magnet of 3-, 4-gradient coil, 5-radio-frequency coil, 6-sick bed;
In Fig. 2 ~ 3: 10-patient body, 20-imaging region, the main magnet of 30-, 40-gradient coil, 50-radio-frequency coil, 60-sick bed.
In Fig. 4: 1a-column; The upper and lower housing cap of 2a-; The semicircle magnet steel of 3a-; The semicircle pole plate of 4a-; The semicircle eddy-current disc of 5a-; The semicircle grading ring of 6a-; 7a-gradient coil; 8a-transmitting coil; 9a-imaging area.
Detailed description of the invention
In order to the technical scheme of the above-mentioned utility model of more detailed statement, below list specific embodiment and carry out Proof Technology effect; It is emphasized that these embodiments are not limited to for illustration of this utility model limit scope of the present utility model.
The nuclear magnetic resonance imaging instrument device that this utility model provides, as shown in Figure 2 to Figure 3, comprise the independent main magnet 30 arranged, be connected to the gradient coil 40 on sick bed 60 and radio-frequency coil 50, described main magnet 30 central authorities are provided with the space stretched into for described sick bed 60, gradient coil 40 and radio-frequency coil 50.This utility model replaces main magnet 30 with independent of the described gradient coil 40 of main magnet 30 and the separate type of radio-frequency coil 50, the structure of gradient coil 40 and radio-frequency coil 50 integral molding, particularly, in the present embodiment, when imaging region 20 size is constant, the interior diameter in the space of described main magnet 30 central authorities is extended to 700 ~ 900mm by 600mm, avoid the closed fear that too narrow space makes patient produce, and this utility model without the need to laying radio-frequency coil 50 in whole main magnet 30, radio frequency detection is carried out to systemic, guarantee that tissue per unit mass is in below margin of safety to power absorption rate.
Preferably, please continue to refer to Fig. 2 and Fig. 3, described nuclear magnetic resonance imaging instrument device also comprises shimming parts (not shown), and described shimming parts are connected on described sick bed 60, and described radio-frequency coil 50 produces magnetic field with main magnet 30; Described gradient coil 40 can increase or weaken the magnetic field intensity that main magnet 30 produces, and makes the spin proton along gradient direction have different magnetic field intensities, thus has dissimilar resonant frequency; Described shimming parts are used for uniform magnetic field.
Preferably, please continue to refer to Fig. 2 and Fig. 3, described gradient coil 40, radio-frequency coil 50 and shimming parts are detachable with described sick bed 60 or packaged type is connected, preferably, described gradient coil 40, the size of radio-frequency coil 50 and shimming parts is corresponding with each body part of patient with position, head imaging as shown in Figure 2 and the foot's imaging shown in Fig. 3, like this, adopt locally, the less gradient coil 40 corresponding with each position of patient body, radio-frequency coil 50 and shimming parts, because the gradient coil 40 of local possesses the good linearity in less space, because this reducing change rate of magnetic density (dB/dt) in safety to physiological constraint, can realize applying at the high efficiency gradient of high-field nuclear magnetic resonance imaging, simultaneously, relative to prior art, the acoustic noise that this utility model is introduced weakens significantly, due to the mechanical force on gradient coil 40 and magnetic field intensity proportional, main magnet 30 is separated with gradient coil 40 by this utility model, limit the intensity of acoustic noise, thus improve comfort level and the mechanical stability of patient, particularly when High field strenghth MRI is applied, effect is more obvious, and, this utility model adopts radio-frequency coil 50 and the shimming parts of local, effectively compensate for the magnetic strength effect increased with high magnetic field intensity, without the radio-frequency coil 50 of whole body, the radio-frequency coil 50 be separated with main magnet 30 is better with body part conformability, as measurement tissue to the index of energy absorption, per unit mass, to power absorption rate (SAR), can control under margin of safety better, in addition, described main magnet 30, gradient coil 40 and the benefit of radio-frequency coil 50 in engineering are: some significantly reducing high-field nuclear magnetic resonance imaging limit substantially, as safety, power attenuation and maintenance cost, therefore the balance in engineering problem can be reduced, thus explore new pulse train design further, obtain new technique and hardware designs.Therefore this utility model presents the motility in space, and the image quality that ensure that.
It should be noted that, structure and the shape of the gradient coil 40 in this utility model, radio-frequency coil 50 and shimming parts are indefinite, Fig. 2 is only schematic diagram, that is, described gradient coil 40, radio-frequency coil 50 and shimming parts respectively with described sick bed 60 for support is laid, the paving mode concrete to it does not limit herein.
Preferably, please continue to refer to Fig. 2 and Fig. 3, described main magnet 30 is the cylinder of the hollow of integral type molding.In this utility model, clinician can before sick bed 60 be pushed in the space of described main magnet 30 central authorities, the position of gradient coil 40, radio-frequency coil 50 and shimming parts is adjusted, makes its patient body 10 of more fitting, thus expand the activity space scope of clinician.
As shown in Figure 4, this utility model adopts single column 1a Open architecture to form single-edge magnetic loop by upper and lower housing cap 2a and single column 1a, single column 1a and upper and lower housing cap 2a is bolted composition building block assembling C type yoke, single column 1a and upper and lower housing cap 2a adopts steel plate or the ZG200-400 cast steel of No. 10 steel matter, and column 1a is trapezoid stand column cross section; On upper and lower housing cap 2a, symmetry is equipped with semicircle magnet steel 3a, semicircle pole plate 4, semicircle grading ring 6a, semicircle eddy-current disc 5a, gradient coil 7 and transmitting coil 8a in order, form imaging area 9a, imaging area 9a is permanent magnet detection zone (namely permanent magnet center zone diameter is the hemisphere territory of 400mm), and magnetic field intensity is 2000 ~ 4000 Gausses; Semicircle pole plate 4a is made up of electrical pure iron DT4, and semicircle magnet steel 3a is made up of N52 ~ N55 high-performance Ne-Fe-B magnet steel; On semicircle pole plate 4, outer end is provided with the semicircle grading ring 6 that electrical pure iron DT4 makes, the semicircle eddy-current disc 5 that Fe-based amorphous alloy soft magnetism 1K101 band is made is provided with in semicircle grading ring 6, eddy current situation: X, Y-direction < 0.4%, Z-direction < 1.0%@100Gs/m; The epoxy plate of circular amorphous eddy-current disc 5 pastes magnetic sheet shimming, the uniformity: during Φ 500mm × 380mm hemisphere, the uniformity: 80ppm; During Φ 400mm × 350mm hemisphere, the uniformity: 20ppm; In semicircle grading ring 6, be provided with gradient coil 7 and transmitting coil 8, gradient coil 7 and transmitting coil 8 can be made one thus reduce symmetrical pole plate gap and play and reduce magnet steel consumption and reduce costs.
The qualitative analysis formula that under characteristic frequency, eddy current produces: i=4K*f*Bm*h*a
2/ 8 ρ; Wherein: i is eddy current, K is form-factor, and f is magnetic frequency, and Bm is magnetic induction peak value, and h is the thickness of pole plate, and ρ is the resistivity of plate material, and a is the pole plate length of side.Can be obtained by above formula, outside the Pass the generation of eddy current and magnetization condition, eddy-current disc amorphous lamination block physical dimension have, also relevant with the resistivity of eddy-current disc material (being inversely proportional to).ρ=40 ~ 50 μ Ω the .cm of stalloy, adds 4% chromium ρ=82 μ Ω .cm in 4.5% silicon steel.Cu-Zn, Ni-Zn ferritic ρ=102 ~ 104 Ω .m, 1K101 amorphous thin ribbon ρ=130 μ Ω .cm.Adopt the eddy-current disc that stalloy is made, eddy current situation: X, Y-direction < 1.0%, Z-direction < 2.5%@100Gs/m; Adopt the eddy-current disc that Fe-based amorphous alloy soft magnetism band 1K101 amorphous thin slice is made, eddy current situation: X, Y-direction < 0.4%, Z-direction < 1.0% 100Gs/m.
The Nd-Fe-B rare earth permanent magnetic material of N52 ~ N55 magnet steel mainly comprises Pr/Nd=0.2 ~ 0.4, Pr
25nd
7529 ~ 31wt%, Co 0.9 ~ 1.5wt%, Cu 0.1 ~ 0.3wt%.Because of Pr
25nd
75be the composition that nature exists, do not need again be separated thus reduce production cost; Have Pr to improve coercivity in magnet steel, Pr adds and reduces the use of heavy rare earth dysprosium, thus reduces production cost; The combining to add and not only increase corrosion resistance and improve again magnet steel magnetic property of CoCu in magnet steel, but it should be noted that Co does not have corrosion resistance lower than 0.9wt%, can remanent magnetism be lowered higher than 1.5wt%.Add Co to add Cu again and can improve corrosion resistance further, but it should be noted that inoperative lower than 0.1wt%, and can remanent magnetism be reduced higher than 0.3wt%.
The open permanent magnet of embodiment 1:C type
Main field strength: 3500 ± 15Gs (magnet constant temperature is 32 DEG C time);
Magnetic material: NdFeB;
Remanent magnetism Br:14.9KGs;
Coercivity bHc: >=10.5KOe;
Maximum magnetic energy product (BH) max:53MGOe;
Magnet steel height: 150mm;
Magnetic direction: vertical, upper pole face is S;
Magnet gap: pole-face is to pole-face 510mm;
Pole plate diameter: 1200mm;
The uniformity: during Φ 500mm × 380mm hemisphere, the uniformity: 100ppm; During Φ 400mm × 350mm hemisphere, the uniformity: 20ppm;
Eddy current situation: magnet has anti-eddy current process (X, Y-direction < 0.4%, Z-direction < 1.0%@100Gs/m)
Magnet outside dimension: wide 1.2m; High 1.7m; Long 2.1m
In sum, the nuclear magnetic resonance imaging instrument device that this utility model provides, comprise the independent main magnet 30 arranged, be connected to the gradient coil 40 on sick bed 60 and radio-frequency coil 50, described main magnet 30 central authorities are provided with the space stretched into for described sick bed 60, gradient coil 40 and radio-frequency coil 50.This utility model structure replacing main magnet 30, gradient coil 40 and radio-frequency coil 50 integral molding independent of the described gradient coil 40 of main magnet 30 and the separate type of radio-frequency coil 50, avoids too narrow space to make patient produce closed fear.Simultaneously this utility model decreases the requirement of existing nuclear magnetic resonance imaging instrument device to magnet material and shielding space, thus reduce further corresponding cost and maintenance cost.
Obviously, those skilled in the art can carry out various change and modification to utility model and not depart from spirit and scope of the present utility model.Like this, if these amendments of the present utility model and modification belong within the scope of this utility model claim and equivalent technologies thereof, then this utility model is also intended to comprise these change and modification.
Claims (1)
1. a nuclear magnetic resonance imaging instrument device, it is characterized in that, comprise imaging region (20), main magnet (30), gradient coil (40), radio-frequency coil (50), sick bed (60), the independent main magnet (30) arranged, be connected to gradient coil (40) and radio-frequency coil (50), the central authorities of described main magnet (30) are provided with the space stretched into for described sick bed (60), gradient coil (40) and radio-frequency coil (50); Wherein said main magnet (30) comprises column (1a), upper and lower housing cap (2a), semicircle magnet steel (3a), semicircle pole plate (4a), semicircle eddy-current disc (5a), semicircle grading ring (6a), gradient coil (7a), transmitting coil (8a), imaging area (9a); Described upper and lower housing cap (2a) and column (1a) are bolted composition building block assembling C type yoke; On described upper and lower housing cap (2a), symmetry is equipped with magnet steel (3a), pole plate (4a), grading ring (6a), eddy-current disc (5a), gradient coil (7a) and transmitting coil (8a) in order, is the formation imaging area, hemisphere territory of 600mm in permanent magnet center zone diameter; On described pole plate, grading ring is equipped with in outer end; Described grading ring is built with eddy-current disc; Gradient coil and transmitting coil be also equipped with in described grading ring, eddy-current disc.
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| CN201420860376.5U CN204410816U (en) | 2014-12-21 | 2014-12-21 | A kind of nuclear magnetic resonance imaging instrument device |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105997078A (en) * | 2016-06-27 | 2016-10-12 | 中国人民解放军第二军医大学 | Nuclear MRI (magnetic resonance imaging) system and method for environment of warship on ocean |
| CN107281653A (en) * | 2017-06-06 | 2017-10-24 | 张坤 | Mri guided radiation therapy apparatus |
| CN109009117A (en) * | 2018-08-23 | 2018-12-18 | 宁波穿山甲机电有限公司 | A kind of ultra-low magnetic resonance imaging system |
-
2014
- 2014-12-21 CN CN201420860376.5U patent/CN204410816U/en not_active Expired - Fee Related
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105997078A (en) * | 2016-06-27 | 2016-10-12 | 中国人民解放军第二军医大学 | Nuclear MRI (magnetic resonance imaging) system and method for environment of warship on ocean |
| CN107281653A (en) * | 2017-06-06 | 2017-10-24 | 张坤 | Mri guided radiation therapy apparatus |
| CN109009117A (en) * | 2018-08-23 | 2018-12-18 | 宁波穿山甲机电有限公司 | A kind of ultra-low magnetic resonance imaging system |
| CN109009117B (en) * | 2018-08-23 | 2023-11-10 | 宁波穿山甲机电有限公司 | Ultralow field magnetic resonance imaging system |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20150624 Termination date: 20151221 |
|
| EXPY | Termination of patent right or utility model |