CN100409022C - An impedance imaging method and apparatus - Google Patents

Abstract

The present invention relates to an impedance imaging method which uses an excitation coil to generate an alternating field. Induction currents are generated in an imaging target according to an electromagnetic induction principle, the distribution of an excitation alternating field is influenced, and magnetic field distribution is measured by using magnetic resonance imaging technique in the imaging target. An imaging device which uses the method comprises excitation coils, a magnetic resonance imaging magnet, a radio frequency emission coil, a gradient coil, a magnetic resonance signal receiving coil, a magnetic resonance imaging system, an excitation current source and a computer, wherein the excitation coils are a pair of Helmholtz coils, and the excitation coils are arranged on an upper pole plate and a lower pole plate of a radio frequency coil of an open type magnetic resonance imaging system. The present invention avoids the influence of the contact impedance and the placing position of an electric pole for an impedance distribution image of the imaging target, overcomes the defect that injection currents generated by a tissue which is similar to an insulator is difficult to penetrate, weakens the pathosis property of an inverse problem of impedance distribution computed by field distribution, solves the problem of imaging resolution, and overcomes the defect that the receiving coil is insensitive for the internal reaction of the imaging target.

Description

A kind of impedance imaging method and device

Technical field

The present invention relates to a kind of medical imaging method, particularly a kind of impedance imaging method and device that utilizes mr imaging technique and magnetic induction principle.

Background technology

Magnetic induction tomography (being called for short MIT) is based on a kind of formation method that different biological tissues has these ultimate principles of electromagnetic property such as different conductivity, specific inductive capacity.As shown in Figure 1, when biological tissue is placed among the excitation field B that is produced by drive coil 1, just induce different eddy current therein, at this moment by receiving coil 2 sense have biological tissue the time magnetic field B _RThe pass of the magnetic field B when not having biological tissue and the conductivity of tissue and specific inductive capacity is:

$\frac{B_R-B}{B}\∝\mathrm{\ω}({\mathrm{\ω\ϵ}}_0{\mathrm{\ϵ}}_r-\mathrm{j\σ})$

Here, ω is the angular frequency of excitation field, ε ₀Be the specific inductive capacity of vacuum, ε _rBe relative dielectric constant, $j=\sqrt{-1},$ σ is a conductivity.By measuring B _RAnd B, just can rebuild the distribution of impedance image of tissue according to corresponding reconstruction algorithm.The problem that this formation method exists is: (1) measures because the disturbance field that induction current produced of imageable target inside is very difficult.Since magnetic test coil be placed on imageable target around, therefore the disturbance field that produces for the induction current of imageable target inside is insensitive, and what that is to say that the detected data of this magnetic test coil react to a great extent is the disturbance field that imageable target surface induction electric current produces; (2) reconstruction algorithm of this formation method adopts the backprojection algorithm in the similar CT imaging usually, and this being similar to is very coarse; (3) the magnetic test coil number in the imageable target placed around is limited, so the raising of its resolution also is very restricted.

Utilize mr imaging technique can detect DISTRIBUTION OF MAGNETIC FIELD in the imageable target, its ultimate principle is to be applied to the phase place that the magnetic-field component parallel with main field that the electric current (steady current or radio-frequency current) on the imaging object produces will influence magnetic resonance image (MRI), and this phase difference is caught by phase encoding.Its detection method is to apply a bipolar current pulse in the spin-echo sequence of a standard, at this moment the magnetic flux density that is parallel to the main field direction that the current impulse that applies produces just is coded on the phase place of magnetic resonance image (MRI), and obtain the magnetic resonance complex pattern and be this moment:

M _cB(x，y)＝M _B(x，y)exp[jγB _zT _C+jφ _c]

Here, M _B(x y) is Mxy, φ _cBe the proper phase of system itself, γ is a gyromagnetic ratio, B _zFor drive coil produces the component along the main field direction in magnetic field, T in tissue _CBe the excitation field application time.Have for the situation that does not have excitation field simultaneously

M _c(x，y)＝M(x，y)exp(jφ _c)

Then the phase change by the caused magnetic resonance image (MRI) of induction field of exciting current is

φ(x，y)＝γB _z(x，y)T _C

The phase place of twice resulting image of imaging process relatively, (x y), thereby just can obtain B from following formula just can to obtain the phase change φ of twice imaging _z(x y), with the imageable target rotation, can obtain the Distribution of Magnetic Field B on two other direction _x(y, z), B _y(x, z), thereby obtain exciting field in imageable target, distribute B (x, y, z).Again by Maxwell equation $\mathrm{\μ}\stackrel{\→}{J}=\▿\×\stackrel{\→}{B}$ Can obtain the electric current distribution in the imageable target.The resolution that this method is measured current density can reach 1 μ A/mm ²This MR imaging method of utilizing is measured Distribution of Magnetic Field, and then the method that obtains electric current distribution is called as the imaging of magnetic resonance current density, is called for short MRCDI.

Based on this method of utilizing mr imaging technique to measure the electric current distribution in the imageable target, the patent No. is US6,397, the United States Patent (USP) of 095 B1 has proposed magnetic resonance impedance tomography (MR-EIT) formation method of a kind of MRCDI technology combined impedance fault imaging (EIT) technology, and imageable target is placed on the high-intensity magnetic field B that is produced by magnet for magnetic resonant imaging ₀In, cable is fixed on the imageable target, and is connected with voltage measuring apparatus with current source, is used in imageable target injection current and measure the surface voltage of imageable target.Display device is used for showing the image of acquisition, and magnetic resonance imaging system is used for controlling the magnetic resonance imaging sequence.Like this, the surface voltage that utilization records and the electric current distribution of imageable target inside, the distribution of impedance image of application equipotential line back projection method reestablishment imaging target.There are some problems in the method for this employing injection current, mainly is: there is contact impedance in the electrode that place on the imageable target surface (1), and therefore, the display case of electrode has influence on the distribution of impedance image to a great extent; (2) if there is current shielding in the imageable target, the skull in the human brain for example, then injection current just is difficult to pass through, thereby influences imaging effect.

Summary of the invention

Technology of the present invention is dealt with problems and is: (1), overcome the influence of contact impedance that the electrode of MR-EIT causes with contacting of imageable target and putting position to imageable target distribution of impedance image, and avoid occurring the problem that injection current that the tissue of similar insulator produces is difficult to pass; (2), overcome the problem of finding the solution the pathosis of this inverse problem of distribution of impedance and solving imaging resolution by field distribution of MIT, the present invention proposes the impedance imaging method and the equipment thereof of the realization biological tissue that a kind of MRCDI technology and magnetic induction principle combine for this reason.

Technical solution of the present invention is: a kind of magnetic resonance magnetic induction impedance imaging method, its characteristics are: it utilizes the excitation induced coil to produce alternating field, in imageable target, produce induction current according to electromagnetic induction principle, adopt the Distribution of Magnetic Field in the mr imaging technique measurement imageable target.

The principle of said method is:

At first measure the magnetic field and the Electric Field Distribution of excitation induced coil imaging region when the no imageable target, store as systematic parameter with the electromagnetic radiation measuring instrument.In imaging process, the imaging sequence of magnetic resonance imaging system is by the current switching of spectrometer system control excitation induced coil, when carrying out the phase encoding of magnetic resonance imaging, apply excitation field, because the difference of the electromagnetic property of each several part in electromagnetic induction phenomenon and the imageable target, the magnetic field of each several part has just produced difference in the imageable target, these differences are reflected on the phase place of magnetic resonance image (MRI) by phase encoding, the magnetic resonance signal that obtains when not applying excitation field relatively, obtain the phase difference of magnetic resonance signal under two kinds of situations, according to the difference of this phase place by equation ΔΦ=γ BT _CCan obtain under the excitation field effect Distribution of Magnetic Field H in the imageable target (r), and then the distribution of impedance image of reestablishment imaging target.

The reconstruction principles illustrated is as follows:

If the time humorous electromagnetic angular frequency that drive coil excites is ω, electromagnetic field satisfies the Maxwell equation group

$\▿\×E=\mathrm{i\ω\μH}---\left(1\right)$

$\▿\×H=J_s+{\mathrm{\σ}}^{*}E---\left(2\right)$

Wherein σ is a conductivity, and ε is a specific inductive capacity, and μ is a magnetic permeability, σ ^*=σ-i ω ε is a complex permittivity, and E is an electric field intensity, and H is a magnetic field intensity, J _SFor the driving source current density, curl is asked at (1) formula two ends, and (2) formula substitution (1) formula is had

$\▿\×\▿\×E-\mathrm{i\ω\μ}{\mathrm{\σ}}^{*}E=\mathrm{i\ω\μ}{J}_s---\left(3\right)$

(3) formula two ends are deducted i ω μ σ _b ^*E, and arrangement can get

$\▿\×\▿\×E-\mathrm{i\ω\μ}{\mathrm{\σ}}_b^{*}E=\mathrm{i\ω\μ}{J}_s+\mathrm{i\ω\μ\Δ}{\mathrm{\σ}}^{*}E---\left(4\right)$

Wherein

$\mathrm{\Δ}{\mathrm{\σ}}^{*}={\mathrm{\σ}}^{*}-{\mathrm{\σ}}_b^{*}---\left(5\right)$

The equation that dyad electricity Green function satisfies is

$\▿\×\▿\×G^e-\mathrm{i\ω\μ}{\mathrm{\σ}}_b{G}^e=\stackrel{\‾}{I}\mathrm{\δ}(r-r^{\′})---\left(6\right)$

Wherein

$G^e(r,r^{\′})=[\stackrel{\‾}{I}+\frac{{\▿}^{\′}{\▿}^{\′}}{K^2}]g(r,r^{\′})$

$g(r,r^{\′})=\frac{e^{-k|r-r^{\′}|}}{4\mathrm{\π}|r-r^{\′}|}$

${\mathrm{<figure-callout\; id="2"\; label="K"\; filenames="C20031011296300111.png"\; state="\{\{state\}\}">K</figure-callout>}}^2=\mathrm{i\&omega;\&mu;}{\mathrm{\&sigma;}}_b^{*}$

Then have

$E=E_b+\mathrm{i\&omega;\&mu;}\underset{V}{\&Integral;}{G}^e(r,r^{\&prime;})\&dtri;{\mathrm{\&sigma;}}^{*}E\left(r^{\&prime;}\right)d{r}^{\&prime;}---\left(7\right)$

Curl is asked on (7) formula both sides, and considered (1) formula, have

$h=H_b+\underset{V}{\&Integral;}{G}^h(r,r^{\&prime;})\mathrm{\&Delta;}{\mathrm{\&sigma;}}^{*}E\left(r^{\&prime;}\right)d{r}^{\&prime;}---\left(8\right)$

$G^h(r,r^{\&prime;})=\&dtri;\&times;G^e(r,r^{\&prime;})$

Order

J(r)＝Δσ ^*E(r)(9)

With (9) substitution (7) and (8), can get following equation

$E\left(r\right)=E_b\left(r\right)+\mathrm{i\&omega;\&mu;}\underset{V}{\&Integral;}{G}^e(r,r^{\&prime;})J\left(r^{\&prime;}\right)d{r}^{\&prime;}---\left(10\right)$

$H\left(r\right)=H_b\left(r\right)+\underset{V}{\&Integral;}{G}^h(r,r^{\&prime;})J\left(r^{\&prime;}\right)d{r}^{\&prime;}---\left(11\right)$

Because H (r) can record H by magnetic resonance method _b(r) can before measuring, obtain, therefore can obtain J (r), because E by (11) by scale _b(r) also can before measuring, obtain (H by scale _b(r) and E _b(r) preserve as systematic parameter, can reuse after the measurement once), E (r) is obtained in J (r) substitution (10), obtain Δ σ by (9) ^*(r), and then by (5) obtain σ ^*(r), thereby can obtain the distribution of impedance image of imageable target, also can obtain the specific inductive capacity distributed image of imageable target.

Adopt the magnetic resonance induction image forming device of said method, its characteristics are: it is made up of excitation induced coil, magnet for magnetic resonant imaging, radio-frequency sending coil and gradient coil, magnetic resonance signal receiving coil, magnetic resonance imaging system, excitation current source and computing machine, and magnetic resonance imaging system comprises imaging spectrometer, radio-frequency (RF) power amplification and gradient power supply.Radio-frequency sending coil generally adopts planar coil, is installed on the last bottom crown of magnet for magnetic resonant imaging, is used for producing the hydrogen proton that excites in the imageable target and resonates.Gradient coil generally also is installed in the last bottom crown of magnet for magnetic resonant imaging, is used for being encoded in the locus of imageable target.Receiving coil covers on the outside of imageable target, is used for accepting the echoed signal of magnetic resonance, and different imageable target can have different receiving coils.It is indoor that magnet for magnetic resonant imaging, radio-frequency sending coil, gradient coil and magnetic resonance signal receiving coil are placed on radio shielding, it is outdoor that magnetic resonance imaging system and excitation current source are placed on radio shielding, is connected with radio-frequency sending coil, gradient coil, magnetic resonance signal receiving coil and excitation induced coil by cable.Imaging sequence is input to imaging spectrometer by computing machine, thereby imaging spectrometer is realized control to radio-frequency coil and gradient coil according to imaging sequence control radio-frequency (RF) power amplification and gradient power supply, and pass through the control excitation current source and realize drive coil is controlled, the magnetic resonance signal receiving coil is delivered to imaging spectrometer with the signal that receives, and carries out image reconstruction by being delivered to computing machine after the imaging spectrometer pre-service.

The excitation induced coil is a pair of Helmholtz coils, is installed in the radio-frequency coil top of bottom crown on the open type magnetic resonance imaging (MRI) system, is used to produce alternation excitation magnetic.Excitation current source utilizes one tunnel control signal of nuclear magnetic resonance spectrometer to realize through power amplification at the driver element of magnetic resonance imaging system, is the drive coil power supply.Power end voltage is 120V, and maximum output current is 80A.If the drive coil spacing is 400mm, then radius also is 400mm, by the thick copper lines coiling of Φ 5mm, the number of turn is 10 circles, exciting current is 80 amperes, then can produce about 20Gs uniformity coefficient and be 0.3% magnetic field in the imaging region of 20cm ball, and this magnetic field is enough to cause the phase change of magnetic resonance signal.

The excitation induced coil produces the uniform unstable magnetic field that is parallel to the main field direction at the imaging region-of-interest, purpose is to make drive coil as far as possible little of ignoring in the magnetic-field component of magnetic field on the both direction beyond the main field that the imaging region-of-interest produces, like this when the magnetic field that the measurement drive coil produces in imageable target, can use along the magnetic-field component of main field direction to replace, thereby in measuring process, not need rotation excitation coil or imageable target.

The concrete operations step of the inventive method is described below:

(1), the excitation induced coil powers up, and utilizes the electromagnetic radiation measuring instrument to measure the Distribution of Magnetic Field H of excitation induced coil imaging area when not having imageable target _b(r) and Electric Field Distribution E _b(r), with H _b(r) and E _b(r) be kept in the computing machine as systematic parameter.

(2), put into imageable target, under the situation that the excitation induced coil does not power up, utilize magnetic resonance imaging system and spin-echo imaging sequence, the magnetic resonance signal when not had exciting field can obtain the phase image Φ of imageable target in the case by Fourier transform ₁(x, y).

(3), put into imageable target, under the situation that the excitation induced coil powers up, utilize magnetic resonance imaging system and corresponding spin-echo imaging sequence, (imaging sequence when not powering up is compared, when being phase encoding, difference applies excitation field), obtain the magnetic resonance signal under the situation that exciting field exists, can obtain the phase image Φ of imageable target in such cases by Fourier transform ₂(x, y).。

(4), the phase place of twice magnetic resonance image (MRI) is compared, can obtain magnetic resonance image (MRI) under the both of these case the phase difference ΔΦ (x, y)=Φ ₂(x, y)-Φ ₁(x, y), according to equation ΔΦ=γ BT _CThe magnetic-field component of excitation field on the main field direction that calculates in the imageable target distributes, and according to the characteristic of Helmholtz coils, the exciting field that the excitation induced coil produces can be similar to by this component and replace.

(5), according to equation (9)～(11)

J(r)＝Δσ ^*E(r)

$E\left(r\right)=E_b\left(r\right)+\mathrm{i\&omega;\&mu;}\underset{V}{\&Integral;}{G}^e(r,r^{\&prime;})J\left(r^{\&prime;}\right)d{r}^{\&prime;}$

$H\left(r\right)=H_b\left(r\right)+\underset{V}{\&Integral;}{G}^h(r,r^{\&prime;})J\left(r^{\&prime;}\right)d{r}^{\&prime;}$

The conductivity that discloses and the relation of Distribution of Magnetic Field, the distribution of impedance image of reestablishment imaging target.

The present invention has following characteristics:

The present invention has avoided contacting of electrode and imageable target, therefore can avoid the influence to imageable target distribution of impedance image of the contact impedance of electrode and putting position, can avoid occurring the problem that injection current that the tissue of similar insulator produces is difficult to pass again.

The present invention can obtain more rich data amount, weakened to a great extent by field distribution and found the solution the pathosis of this inverse problem of distribution of impedance and the problem that solves imaging resolution, can solve receiving coil again the insensitive problem of imageable target internal-response.

The present invention more can truly reflect objective problem than backprojection reconstruction algorithm in theory fully taking into account the distribution problem of exciting field in nonhomogeneous media on the reconstruction algorithm in addition.

Description of drawings

Fig. 1 is the magnetic induction image schematic diagram, and 1 is drive coil, and 2 is receiving coil, and 3 is imageable target, and 4 is interior tissue;

Fig. 2 is the synoptic diagram of embodiment of using the magnetic resonance magnetic induction image device of the inventive method, wherein 10 is the excitation induced coil, 20 is magnet for magnetic resonant imaging, radio-frequency sending coil and gradient coil, 30 is the magnetic resonance signal receiving coil, 40 is magnetic resonance imaging system, 50 is excitation current source, and 60 is computing machine.

Embodiment

Fig. 2 is the specific embodiment of the magnetic resonance magnetic induction image device of application the inventive method.As shown in Figure 2:

The excitation induced coil 10 of a pair of Helmholtz's formula is installed in the last bottom crown place of magnet for magnetic resonant imaging 20, spacing between two coils equals the radius of coil, here radius=spacing=400mm, thick copper lines coiling by Φ 5mm, the number of turn is 10 circles, exciting current is 80 amperes, then can produce about 20Gs uniformity coefficient and be 0.3% magnetic field in the imaging region of 20cm ball.One tunnel control signal of nuclear magnetic resonance spectrometer is carried out the current source 50 of power amplification as drive coil, and the terminal voltage of this current source is 120V, maximum output current 80A.Magnetic resonance imaging system 40 comprises imaging spectrometer, radio-frequency (RF) power amplification and gradient power supply.

Its course of work is: imaging sequence is input to imaging spectrometer by computing machine 60, thereby imaging spectrometer is realized control to radio-frequency coil and gradient coil according to imaging sequence control radio-frequency (RF) power amplification and gradient power supply, and by controlling excitation current source 50 realizations to drive coil 10 controls, magnetic resonance signal receiving coil 30 is delivered to imaging spectrometer with the signal that receives, and carries out image reconstruction by being delivered to computing machine 60 after the imaging spectrometer pre-service.Drive coil 10 produces the uniform unstable magnetic field that is parallel to the main field direction at the imaging region-of-interest, and the frequency of operation of drive coil is 2KHz.When carrying out the phase encoding of magnetic resonance imaging, apply excitation field by drive coil, because the difference of the electromagnetic property of each several part in electromagnetic induction phenomenon and the imaging region, the magnetic field of each several part has just produced difference in the imaging region, these differences are reflected on the phase place of magnetic resonance image (MRI) by phase encoding, the magnetic resonance signal that obtains when not applying excitation field relatively obtains the phase difference ΔΦ of magnetic resonance signal in both cases, according to the difference of this phase place by equation ΔΦ=γ BT _CCan obtain under the excitation field effect Distribution of Magnetic Field H in the imageable target (r), again according to the distribution of impedance image of equation (9)～(11) reestablishment imaging target.

The concrete operations step is described below:

1, excitation current source 50 powers up for drive coil 10, measures the electric field and the Distribution of Magnetic Field of the imaging region when not having imageable target with the electromagnetic radiation measuring instrument, and is kept in the computing machine 60.

2, imageable target is put into imaging region, apply the spin-echo imaging sequence, the magnetic resonance image (MRI) when obtaining excitation field and not existing.

3, imageable target is put into imaging region, drive coil 10 powers up, and applies the spin-echo imaging sequence, the magnetic resonance image (MRI) when obtaining excitation field and existing.

4, compare the phase place of twice magnetic resonance image (MRI), obtain the distribution of excitation field in imageable target.

5, calculate electric current distribution in the imageable target according to equation (11).

6, calculate Electric Field Distribution in the imageable target according to equation (10).

7, calculate telegram in reply conductance poor of imageable target and air according to equation (9).

8, calculate the telegram in reply conductance of imageable target according to equation (5).Thereby obtain the distribution of impedance image of imageable target.

The inventive method adopts the mode of excitation induced effectively to avoid the shielding effect of megohmite insulant in the imageable target, utilize the mode of magnetic resonance imaging to measure the distribution of magnetic field in imageable target, can effectively solve and externally measured uneven problem be reflected in imageable target inside, the data volume that measures simultaneously is rich

Richness can also obtain the structural information of imageable target when obtaining Distribution of Magnetic Field, effectively improved the precision of reconstructed image, makes image quality step major step forward.

Claims (3)

1. impedance imaging method is characterized in that at first measuring with the electromagnetic radiation measuring instrument magnetic field and the Electric Field Distribution of excitation induced coil imaging region when the no imageable target, stores as systematic parameter; In imaging process, the imaging sequence of magnetic resonance imaging system stress be encouraged the current switching of coil by magnetic resonance spectrum instrument system sense of control, when carrying out the phase encoding of magnetic resonance imaging, apply excitation field, because the difference of the electromagnetic property of each several part in electromagnetic induction phenomenon and the imageable target, the magnetic field of each several part has just produced difference in the imageable target, these differences are reflected on the phase place of magnetic resonance image (MRI) by phase encoding, the magnetic resonance signal that obtains when not applying excitation field relatively, obtain the phase difference of magnetic resonance signal under two kinds of situations, according to the phase difference of magnetic resonance signal under the both of these case, by equation ΔΦ=γ BT _CCan obtain under the excitation field effect Distribution of Magnetic Field H in the imageable target (r), herein T _CImplication be the time that excitation field applies, and then the distribution of impedance image of reestablishment imaging target.

2. according to the said impedance imaging method of claim 1, it is characterized in that the operation steps of the method is:

(1), the excitation induced coil powers up, and utilizes the electromagnetic radiation measuring instrument to measure the Distribution of Magnetic Field H of excitation induced coil imaging area when not having imageable target _b(r) and Electric Field Distribution E _b(r), with H _b(r) and E _b(r) be kept in the computing machine as systematic parameter;

(2), put into imageable target, under the situation that the excitation induced coil does not power up, utilize magnetic resonance imaging system and spin-echo imaging sequence, the magnetic resonance signal when not had exciting field can obtain the phase image Φ of imageable target in the case by Fourier transform ₁(x, y);

(3), put into imageable target, under the situation that the excitation induced coil powers up, utilize magnetic resonance imaging system and corresponding spin-echo imaging sequence, obtain the magnetic resonance signal under the situation that exciting field exists, obtain the phase image Φ of imageable target in such cases by Fourier transform ₂(x, y);

(4), the phase place of twice magnetic resonance image (MRI) is compared, obtain magnetic resonance image (MRI) under the both of these case the phase difference ΔΦ (x, y)=Φ ₂(x, y)-Φ ₁(x, y), according to the equation ΔΦ (x, y)=γ B (x, y) T _CThe excitation field that calculates in the imageable target distributes in the magnetic-field component of main field direction, herein T _CBe the time that excitation field applies, according to the characteristic of Helmholtz coils, the exciting field that the excitation induced coil produces can be similar to by this component and replace;

(5), according to following equation:

J(r)＝Δσ*E(r)

$E\left(r\right)=E_b\left(r\right)+\mathrm{i\&omega;\&mu;}\underset{V}{\&Integral;}{G}^e(r,r^{\&prime;})J\left(r^{\&prime;}\right){\mathrm{dr}}^{\&prime;}$

$H\left(r\right)=H_b\left(r\right)+\underset{V}{\text{\&Integral;}}{G}^h(r,r^{\&prime;})J\left(r^{\&prime;}\right){\mathrm{dr}}^{\&prime;}$

The conductivity that discloses and the relation of Distribution of Magnetic Field, the distribution of impedance image of reestablishment imaging target.

3. application rights requires the device of 1 or 2 said impedance imaging methods, comprise magnet for magnetic resonant imaging, radio-frequency coil and gradient coil, magnetic resonance signal receiving coil (30), magnetic resonance imaging system (40) and computing machine (60), it is characterized in that it also comprises excitation induced coil (10), excitation current source (50); Excitation induced coil (10) is a pair of Helmholtz coils, is installed in the radio-frequency coil top of bottom crown on the open type magnetic resonance imaging (MRI) system; Excitation current source (50) carries out power amplification with one tunnel control signal of nuclear magnetic resonance spectrometer to be realized.

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