Frequency Mixing Magnetic Detection Scanner for Imaging Magnetic Particles in Planar Samples


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A scanner for imaging magnetic particles in planar samples was developed using the planar frequency mixing magnetic detection technique. The magnetic intermodulation product response from the nonlinear nonhysteretic magnetization of the particles is recorded upon a two-frequency excitation. It can be used to take 2D images of thin biological samples.

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Hong, H., Lim, E. G., Jeong, J. c., Chang, J., Shin, S. W., Krause, H. J. Frequency Mixing Magnetic Detection Scanner for Imaging Magnetic Particles in Planar Samples. J. Vis. Exp. (112), e53869, doi:10.3791/53869 (2016).


The setup of a planar Frequency Mixing Magnetic Detection (p-FMMD) scanner for performing Magnetic Particles Imaging (MPI) of flat samples is presented. It consists of two magnetic measurement heads on both sides of the sample mounted on the legs of a u-shaped support. The sample is locally exposed to a magnetic excitation field consisting of two distinct frequencies, a stronger component at about 77 kHz and a weaker field at 61 Hz. The nonlinear magnetization characteristics of superparamagnetic particles give rise to the generation of intermodulation products. A selected sum-frequency component of the high and low frequency magnetic field incident on the magnetically nonlinear particles is recorded by a demodulation electronics. In contrast to a conventional MPI scanner, p-FMMD does not require the application of a strong magnetic field to the whole sample because mixing of the two frequencies occurs locally. Thus, the lateral dimensions of the sample are just limited by the scanning range and the supports. However, the sample height determines the spatial resolution. In the current setup it is limited to 2 mm. As examples, we present two 20 mm × 25 mm p-FMMD images acquired from samples with 1 µm diameter maghemite particles in silanol matrix and with 50 nm magnetite particles in aminosilane matrix. The results show that the novel MPI scanner can be applied for analysis of thin biological samples and for medical diagnostic purposes.


Magnetic nanoparticles (MNP) have found widespread applications in molecular biology and in medicine, i.e., for manipulation of biomolecules and single cells1, for selectively labeling target entities for detection,2, 3 for chromatin modulation,4 and for mRNA isolation and cancer treatment.5 Due to their superparamagnetic properties, they are especially useful for medical imaging. They can serve, for instance, as contrast agents or tracers for Magnetic Resonance Imaging (MRI) or for susceptibility imaging using Superconducting Quantum Interference Device (SQUID) detectors. 2, 6 The superparamagnetic nanoparticles yield a good contrast to the different tissues of the human body which are dia- or paramagnetic.7 Thus, the particles can conveniently be used to acquire medical images of human body parts with relatively good spatial resolution and sensitivity.8

The Magnetic Particle Imaging (MPI) technique introduced by Gleich and Weizenecker9 makes use of the nonlinearity of the particle's magnetization. At zero or weak magnetic field bias, the response of MNP to an ac excitation of frequency f is strong due to their large susceptibility. In particular, the particle's nonlinear magnetization gives rise to the generation of harmonics n·f, with n = 2, 3, 4 … At high magnetic field bias, the harmonic response becomes weak because the particles are magnetically saturated. In the MPI technique, the sample is completely magnetized except for a field-free line (FFL) or a field-free point (FFP). Only particles situated close to this line or point will contribute to the nonlinear response of the sample. With the movement of a FFP and employment of suitable receiver coils, Gleich and Weizenecker acquired MPI images with a spatial resolution of 1 mm.

In order to obtain information on the spatial distribution of MNP, two methods are usually employed, the mechanical movement of the sensor with respect to the sample, or movement of the FFL/FFP by means of electromagnets.2, 3 In the latter case, image reconstruction techniques like harmonic-space MPI3 or X-space MPI10, 11, 12 are required. The spatial resolution of MPI is determined by the convolution properties of excitation and detection coils as well as by the characteristics of the magnetic field gradient. This allows image reconstruction algorithms to obtain an improved resolution over the native resolution, which is determined by size and distance of the pickup coils as well as by the magnetic field distribution governed by Maxwell's equations.

A MPI scanner is usually comprised of a strong magnet for magnetizing the whole sample, a controllable coil system for steering a FFL or FFP across the sample, a high frequency excitation coil system, and a detection coil system for picking up the nonlinear response from the sample. The FFL/FFP is continuously moved through the sample volume while the harmonic response from this unsaturated sample region is recorded. In order to avoid the problem of fitting the specimen into the scanner, a single-sided MPI scanner has been demonstrated by Gräfe et al.13, however at the expense of reduced performance. Best results are obtained if the sample is surrounded by the magnets and coils. Because the sample has to be fully magnetized except for the FFL/FFP region, the technique requires relatively large and strong magnets with water cooling, leading to a rather bulky and heavy MPI system.

Our approach is based on frequency mixing at the non-linear magnetization curve of superparamagnetic particles.14 When super-paramagnets are exposed to magnetic fields at two distinct frequencies (f1 and f2), sum frequencies representing a linear combination m·f1 + n·f2 (with integer numbers m, n) are generated. It was shown that the appearance of these components is highly specific to the nonlinearity of the magnetization curve of the particles.15 In other words, when the MNP sample is simultaneously exposed to a driving magnetic field at frequency f2 and a probing field at frequency f1, the particles generate a response field at frequency f1 + 2·f2. This sum frequency would not be existent without the magnetically nonlinear sample, therefore the specificity is extremely high. We called this method "frequency mixing magnetic detection" (FMMD). It has been experimentally verified that the technique yields a dynamic range of more than four orders of magnitude in particle concentration.14

In contrast to typical MPI instrumentation, the planar frequency mixing magnetic detection (p-FMMD) approach does not require to magnetize the sample close to saturation because the generation of the sum frequency component f1 + 2·f2 is maximum at zero static bias field.14 Therefore, the need for strong and bulky magnets is alleviated. In fact, the outer dimensions of the measurement head are only 77 mm × 68 mm × 29 mm. For comparison, MPI setups are typically meter-sized.7 The drawback, however, is that the technique is restricted to planar samples with a maximum thickness of 2 mm in the current setup. The sample has to be scanned relatively to the two-sided measurement head. A re-construction allowing for thicker samples is possible, but has to be traded in for a loss of spatial resolution.

Based on this FMMD technique, we present a special type of MPI detector for planar samples, the so-called "planar frequency mixing magnetic detection" (p-FMMD) scanner. The principle has been recently published.17 In this work, we focus on the methodology of the technique and present protocols how to set up such a scanner and how to perform scans. It has been shown that MPI can be applied for medical diagnostic purposes such as cardiovascular or cancer imaging.16, 18, 19 Therefore we believe that the new MPI scanner can be used for a broad range of potential applications, e.g., for measuring magnetic particle distribution in tissue slices.

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1. Design a Planar FMMD Measurement Head

  1. Choose a coil scheme for the measurement head. Select a configuration according to Figure 1, consisting of two pickup coils above and two below the sample in a (-, +, +, -) sequence, with the sample sitting in the center between the two (+) coils. The sign denotes the direction of winding, i.e., (+) for clockwise and (-) for counterclockwise. Thus, the sensitivity of the pickup coils becomes almost homogeneous across the sample thickness.
    1. Place the excitation coils such that the directly induced signal in the pickup coils cancels out in order to prevent saturation of the preamplifier and achieve maximum sensitivity to the sample. Other configurations that fulfill these basic design rules can be devised.
  2. Specify the maximum sample thickness. Here, use 2 mm.
    1. Choose the diameter and length of the pickup coils similar to the maximum sample thickness. Here, an inner diameter of 2 mm was chosen, which yields an average diameter of 3.7 mm for the height of windings of 1.7 mm. The coil width is 4 mm.
    2. Choose the wire diameter and the number of windings of the pickup coils such that the total impedance of all pickup coils approximately matches the input impedance of the preamplifier. This condition imposes restrictions on the detection frequency. In the case of a operational amplifier with an optimum input impedance of 1,100 Ω, all four pickup coils have 600 windings of 0.08 mm dia. enameled copper wire, yielding a total Ohmic series resistance of 95.3 Ω and a total inductance of 1.9 mH, which gives 919 Ω impedance.
  3. Prepare the high frequency excitation coils17 such that the magnetic field at the sample's location ideally amounts to about 0.5 mT. For instance, if the inner radius of the coil is 3.8 mm and the width is 8.5 mm, wind 476 windings of 0.1 mm diameter wire. Here, a field of 0.4 mT was achieved at f1 = 76,550 Hz.
  4. Prepare the low frequency excitation coils17 such that the magnetic field at the sample's location is about 5 mT. For instance, if the inner radius of the coil is 5 mm and the width is 8.5 mm, wind 2,000 windings of 0.12 mm diameter wire. The setup yielded 5 mT at f2 = 61 Hz.

Figure 1
Figure 1. Schematic drawing of the p-FMMD set-up. Two measurement heads are electronically connected to each other. The sample is placed in the space between the heads. Detection coils (+) measure the sample signal, counter-wound detection coils (-) serve as reference to cancel out the direct field from the high frequency excitation coils. Amp - preamplifier, x - mixer, LPF - low pass filter, DAQ - data acquisition. Please click here to view a larger version of this figure.

2. Construct the Measurement Head

  1. Construct the p-FMMD such that two sets of excitation and detection coils are attached above and below the sample. Each set of coils consists of a low frequency driver coil, a high frequency excitation coil, and a differential detection coil comprising two oppositely wound pickup coils in axial gradiometer configuration.
    1. Allow for an adjustability of at least one excitation coil relative to the differential detection coil in order to be able to balance out direct induction of the high frequency excitation into the detection coil. For instance, mount the excitation coil on a thread which allows relative movement of the excitation coil versus the detection coil. A schematic diagram of the p-FMMD is shown in Figure 1. Figure 2 depicts a technical drawing and a photograph of the setup. Detailed parameters of the coils are listed in Table 1.
  2. Mount the coil sets above and below the sample on a rigid support, with coaxial orientation, see Figures 1 and 2. Make sure that the two coil sets do not vibrate relative to each other.
  3. Adjust the high frequency balance of the measurement head by applying the high frequency excitation current to the respective excitation coil set, varying the relative position between them, and simultaneously measuring the detected signal at this frequency at the detection coil set, using equipment such as an oscilloscope or a lock-in amplifier.
    1. Adjust the directly induced voltage as low as a few millivolts, i.e., more than 1,000-fold suppression of direct induction. Determine the limit of adjustability by observing the phase shift between excitation current and detected voltage. At the minimum, the induced voltage is 90° phase-shifted as compared to direct induction.

Figure 2
Figure 2. Technical drawing and photo of p-FMMD head. Cross-sections along a vertical plane (top left) and a horizontal plane (bottom left) are shown as well as a photograph of the opened measurement head before coil winding. 1 - Aluminum support, 2 - coil former for detection coils, 3 - threaded coil former for excitation coils which can be moved up/down by rotation, 4 - sample support plates, 5 - aluminum lids, 6 - sample stopper support, 7 - stopper in x direction, 8 - stopper in y direction. 6 - 8 are removed for scanning. The size of the p-FMMD head is 77 mm × 68 mm × 29 mm. Please click here to view a larger version of this figure.

3. Set up Measurement Electronics

  1. Configure the excitation section, consisting of the two oscillators and power amplifiers for both low frequency driver coil and high frequency excitation coil.
    1. Set up the low frequency driver section, comprising an oscillator and a power amplifier for the low frequency f2. Calculate the power of the amplifier such that it delivers the required current to produce the field of about 5 mT in the driver coil. Here, use a Direct Digital Synthesis (DDS) chip as programmable oscillator. Employ a high-speed buffer as power amplifier.
    2. Set up the high frequency excitation section, comprising an oscillator and a power amplifier for the high frequency f1. Set up the power amplifier such that it delivers the required current to produce the field of about 0.5 mT in the excitation coil. Use a DDS chip and a high-speed buffer as oscillator and power amplifier, respectively.
  2. Configure the detection section, consisting of a preamplifier, a first mixer to demodulate from the high frequency f1, an intermediate amplifier and filter, a second mixer to demodulate from twice the low frequency 2·f2, and a final filter and output driver. Alternatively, use two lock-in amplifiers to implement the detection electronics.
    1. Set up the preamplifier stage. Select the input operational amplifier (OP), considering the impedance of the detection coil and the gain-bandwidth product. Perform the noise optimization procedure, taking into account the specified voltage noise and current noise of the OP, as explained in Ref. 10. Select a high-speed low-noise operational amplifier with an amplification of about 100 in the first stage. The subsequent stage is uncritical, but check that the output signal remains in the voltage range, i.e., not distorted due to overloading. Here, use a low-noise JFET input operational amplifier with 4.3-fold amplification.
    2. Set up the first demodulation stage, multiplying the amplified signal with the high frequency f1. Use an analog multiplier chip and reference it from a second separate DDS chip in order to realize an adjustable phase for demodulation. Alternatively, use a lock-in amplifier as preamplifier (3.2.1), first demodulator (3.2.2) and high frequency generator (3.1.2).
    3. Set up the intermediate amplification and filtering stage. Implement a low-pass filter such that the signal frequency at 2·f2 passes undisturbed while the spurious high frequency components at f1 and 2·f1 are efficiently suppressed. Choose a suitable intermediate amplification, for instance by selecting two general-purpose operational amplifiers with a total amplification of about 100.
    4. Set up the second demodulation stage, multiplying the filtered and amplified signal with twice the low frequency 2·f2. Use an analog multiplier chip and reference it from a fourth separate DDS chip in order to realize an adjustable phase for demodulation. Alternatively, use a lock-in amplifier capable of second harmonic demodulation as intermediate amplifier (3.2.3), second demodulator at second harmonic (3.2.4) and low frequency generator (3.1.1).
    5. Set up the final amplification and filtering stage. Implement a low-pass filter such that the signal frequency at the scanning frequency passes undisturbed while the spurious high frequency components at 4·f2 are efficiently suppressed. Choose a suitable final amplification, considering the desired output voltage range. Use two general-purpose operational amplifiers with a total amplification of about 10.

4. Set up 2D Scanner

  1. Mount a 2D scanner so that the motion plane is perpendicular to the coil's axis.
  2. Control the 2D scanner and synchronously acquiring the output voltage from the measurement electronics in order to obtain a 2D image of the FMMD signal of the planar sample using a homemade script written in the programming language Python.

5. Prepare Sample

  1. Use magnetite particles with diameters of 50 nm and 100 nm and maghemite particles with a diameter of 1 µm of which concentration is 25.0 mg/ml. Wash the solution by dissolving the magnetic particles in water, separating them using a magnet and discarding the water. Repeat the procedure three times. Dilute the magnetic particle solution to one tenth with distilled water.
  2. Prepare paper pellet samples with 2.0 mm diameter by punching pieces of absorptive blotting paper using a biopsy punch. Soak them in magnetic bead solution of different concentrations for 30 sec and let them dry in air. Here, use concentrations of 0.04, 0.2, 1, 5, and 25 mg/ml of 100 nm sized particles.
  3. Prepare a sample using a nitrocellulose membrane of size 2.0 mm × 18.0 mm. Soak the membrane with the undiluted 1 µm diameter particle solution. Prepare one sample by soaking the membrane evenly, and another one by making a concentration gradient. Do this by soaking the ends of the membrane in beads solution with different concentration, resulting in the concentration gradient (Figure 5).
  4. Prepare a sample in a capillary tube of 10 µl volume, outer diameter 400 µm, length 40 mm. Fill the capillary tube with undiluted 50 nm diameter particle solution. Prepare a second microtube with 20x diluted solution (mix 100 µl of undiluted solution with 1.9 ml of water).

6. Perform 2D FMMD Scan

  1. Select scanning area according to planar dimensions a × b of the sample. Enter the values in the scanning software.
  2. Select stepping direction. Usually, the shorter of the two planar dimensions, let us call it b, will be selected as stepping direction because that requires less steps and thus less acceleration and deceleration phases.
  3. Select scanning speed v, with consideration of signal reduction due to low-pass filtering, see discussion. Adjust the speed to a value between 1 and 7 mm/sec. Enter the value in the scanning software.
  4. Select stepping distance Δb, taking into account that it need not be much smaller than the achievable spatial resolution, and the total scanning time t which will be at least t = a/v·bb+1). Enter the stepping distance in the software.
  5. Mount the sample on the 2D scanner. Fix it on the plastic plate using adhesive tape.

Figure 3
Figure 3. Photo of p-FMMD measurement setup. The sample is affixed with adhesive tape on the plastic carrier moved by the motor stage (left). Then the sample is scanned in the p-FMMD head (right). Please click here to view a larger version of this figure.

  1. Perform the scan by pressing the start button. The scans of Figures 5 and 6 cover a 20.0 mm (x axis) × 25.0 mm (y axis) region, i.e., six 25 mm long traces were scanned along the y axis, with 4.0 mm steps in x direction, at a stage speed of 1.0 mm/sec. This amounts to a scanning time of about 2 min.

Figure 4
Figure 4. Graphical User Interface of the scanning software. The scan parameters are entered here. The measurement is started by pressing the red button.

7. Image Processing

  1. Convert the raw data to matrix form using a homemade script in python. Log the raw data of the whole scan together with extra values in a 2-column comma-separated values (CSV) format file. The extra column indicates the capturing the corresponding data during the stepping motion. The script segments the raw data column at each change of the extra column value and removes the data segments during stepping motion. It also constructs the resultant matrix by putting the remaining consecutive segments into rows or columns of the matrix and writes the matrix into a CSV format file.
    Note: p-FMMD images of this study are generated using a python script. The pyplot.contour function and the pyplot.imshow function from the matplotlib library for python are cumulatively used for preparation of the contours and the background colors, respectively.

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Representative Results

Figure 5a shows the calculated sensitivity distribution of the inner double-differential detection coil as a function of the coordinates x and y in the sample plane. It was calculated in an inverse approach by determining the superposition of the magnetic fields at all points (x, y) in the central plane generated by all four detection coils. In reverse, this determines the detection coil's sensitivity to a magnetic moment at each of these points. The calculation was performed by approximating the coils as long coils of negligible height. Thus, the sensitivity distribution depicted in Figure 5a represents the sensitivity map in the scanning plane, the so-called point spread function (PSF). In a similar fashion, Figure 5b shows the sensitivity as a function of the axial coordinate z and the radial coordinate r (r2 = x2 + y2), thus giving a vertical mapping of the sensitivity in the slit of the measurement head. The origin x = 0 and y = 0 is located exactly in the center of the detection coil. The spacing between the centers of the upper and lower detection coil is 2 mm. The coil parameters are listed in Table 1. Figure 5c shows the result of an experimental scan over the string-type line sample prepared according to protocol 5.2. For comparison, a sensitivity trace was calculated by numerically integrating the point spread function depicted in Figure 5a over a 2 mm wide ideal line. The agreement is good, except that the negative shoulders in the calculated signal are not observed experimentally. In the simulation, these negative parts originate from the negative contributions from the reference coils which are more in the far-field regime than the detection coils next to the sample. We believe the negative contribution is overestimated in simulation because the coils are approximated with negligible height of windings.

Figure 5
Figure 5. Performance of the measurement head. Calculated sensitivity distribution of the measurement head (a) as a function of the planar coordinates x and y for z = 0, (b) as a function of the axial coordinate z and the radial coordinate r. The sensitivity is given relatively to the center between the upper and lower detection coil at x = 0, y = 0 and r = 0. (c) Comparison of measured and simulated sensitivity. Please click here to view a larger version of this figure.

We calculated the physical detection limit of the coil at measurement frequency f1 = 76.56 kHz with respect to magnetic moments at the center of the measurement head. For the calculation, the parameters of the inner coil were taken as listed in Table 1, assuming a filling factor (i.e., the copper fraction in the windings cross section) of KF = 0.5. We obtained a magnetic moment sensitivity of m0/√f = 1.8·10-14 Am2/√Hz. For 1 sec measurement time, this amounts to a resolvable minimum magnetic moment of m0 = 7.3·10-14 Am2. This value is comparable than the detection limit that can be obtained with a standard 8 mm diameter measurement head.14

Figure 6a shows the signal intensity as a function of the concentration of magnetic beads solution. The scanning speed was 1.0 cm/min. The concentration of the paper pellets prepared according to protocol 5.2 was varied from 0.04 to 25.0 mg/ml. The error bars denote the standard deviation of the FMMD measurement. The results showed a strong correlation between the concentration of magnetic beads and the signal from the detector. The coefficient of determination R2 of the linear regression was evaluated as 0.98. Figure 6b shows the measured relationship between the speed of the scanning stage and the signal intensity measured with the 5 mg/ml paper pellet sample according to protocol 5.3. It was found that higher signals can be obtained at lower speed.

Figure 6
Figure 6. Calibration. Normalized calibration curve of (a) the p-FMMD measurement using different concentrations of magnetic beads. As samples, paper pellets with 2.0 mm diameter were prepared using a biopsy punch, soaked in magnetic particle solution of different concentrations (see protocol 5.3). The measurement head passed the paper pellets with different concentrations of MP. The speed of the stage was adjusted to 1.0 mm/sec. (b) Signal intensity as function of the speed of the XY stage for the 5.0 mg/ml paper pellet sample. Please click here to view a larger version of this figure.

Figure 7 shows a photograph of membrane-type samples prepared according to protocol 5.4 and the reconstructed p-FMMD image obtained from it. The picture area as well as the scanning area are both 20 mm × 25 mm. The comparison of the p-FMMD scan with the optical image of the sample clearly demonstrates the feasibility to use the p-FMMD as MPI scanner. However, the p-FMMD scans are somewhat broader than the real objects. This broadening can be mainly attributed to the sensitivity profile of the measurement head. As shown in Figure 5a, the measurement of a magnetic particle distribution is broadened by this distribution even to ±2.0 mm from the center of the measurement heads.

Figure 7
Figure 7. 2D FMMD scan. (a) Photograph of the string type sample. The sample was prepared using a nitrocellulose Membrane soaked with 1 µm diameter maghemite particle solution SiMAG-Silanol see protocol 5.4. (b) Reconstructed MPI image, size 20 mm × 25 mm. The sample is continuously scanned in y direction and consecutively stepped in x direction by 4 mm. Please click here to view a larger version of this figure.

A second sample was prepared, consisting of two microtubes filled with different magnetic particle concentration, as described in protocol 5.5. Figure 8 shows a photograph of the sample and the reconstructed p-FMMD image, both with a size of 20 mm × 25 mm. This example demonstrates that concentrations differing by a factor of 20 can be well imaged with clearly discernible image features.

Figure 8
Figure 8. 2D FMMD scan. (a) Photograph of two microtubes of 10 µl volume with different sample concentrations of fluid MAG-Amine, see protocol 5.5. (b) Reconstructed MPI image, size 20 mm × 25 mm. The sample is continuously scanned in y direction and consecutively stepped in x direction by 4 mm. Please click here to view a larger version of this figure.

Coil dimensions Windings Coil below sample Coil above sample
Coil R1 [mm]a W [mm]b H [mm]c No. of windings Wire-Ø [mm] R [Ω]d L [mH]e R [Ω]d L [mH]e
Measurement 1.0 4.0 1.7 2 × 600 0.08 47.67 0.95 47.66 0.95
Excitation 3.8 8.5 1.0 476 0.10 29.90 1.56 29.70 1.45
Driver 5.0 8.5 5.0 2,000 0.12 190.75 36.90 141.28 37.90
aR1 is the inner radius of the coil. The average radius is R1+H/2, the outer radius is R1+H. 
bW is the width of the coil, i.e., the cross section of the windings.
cH is the height of the coil windings.
dR denotes the Ohmic resistance at DC. In case of the measurement coils, it is the series resistance of both coils.
eL denotes the inductance, measured with an inductance meter at 1 kHz.

Table 1. Coil Parameters. Dimensions and windings of the coils of the measurement head.

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The measurement technique utilizes the nonlinearity of the magnetization curve of the superparamagnetic particles. The two-sided measurement head simultaneously applies two magnetic excitation fields of different frequency to the sample, a low frequency (f2) component to drive the particles into magnetic saturation and a high frequency (f1) probe field to measure the nonlinear magnetic response. In particular, both harmonics of the incident fields, m·f1 and n·f2, and sum frequencies, m·f1 + n·f2 (with integer numbers m, n), are generated. These intermodulation products are detected by the differentially wound pickup coil. The reference coils do not pick up these signals because they are located far away from the sample. They serve for suppression of the directly induced high frequency excitation which would otherwise saturate the preamplifier. Thus, the tiny sum-frequency signal due to the presence of super-paramagnetic materials becomes measurable and quantifiable. In the readout electronics, only the intermodulation product at sum frequency f1 + 2·f2 is demodulated because it is the strongest nonlinear component which is present without static bias field. It was shown that this technique allows fast processing and a very large dynamic detection range. Details of the FMMD principle and the readout electronics are described in detail in Ref. 10.

The measurement results shown in Figure 6 reveal that the p-FMMD signal depends on the speed of the scanning stage and on the concentration of the magnetic particles. Consequently, spatial resolution and detection limit of the technique are also speed- and concentration-dependent. We attribute this finding to the signal reduction of the low pass filter at the output of the two-stage lock-in detection of the readout electronics. Previous research on MPI also showed that the spatial resolution is dependent on the parameters speed of gradient strength, particle diameter, volume of the magnetic core and mechanical speed of the stage.20 Our findings are consistent with these results.

Our 2D scanning method differs considerably from the conventional MPI technique based on generating a Field Free Point (FFP) or Field Free Line (FFL), even though the detection principle based on the non-linear signal from superparamagnets is similar.3, 21 Although conventional MPI has advantages over the new p-FMMD technique, such as the simultaneous 3D analysis without mechanical movement of sample or system7, the new MPI scanner does not need big magnets to generate a strong field. We believe that both the conventional MPI scanner and the p-FMMD scanner have their specific advantages. The advantage of the p-FMMD scanner is its simplicity and its small dimensions. There is no need for employing large gradient coils and no need for cooling coils. The sample size in x and y direction are not limited by the technique, just by the scanner and the support. However, the technique is only applicable to sufficiently thin samples that fit between the detection coils. It requires movement of the sample relatively to the measurement head, whereas standard MPI utilizes electrically controlled scanning of the FFL/FFP without sample movement.

MPI is a relatively new technique that has a variety of potential applications in many scientific and industrial fields. It has been shown that its spatial resolution is comparable with that of other medical imaging modalities. In this study, we introduced a new technique called p-FMMD to perform MPI of planar samples. Compared to other MPI scanners, it does not require the generation of a FFL or FFP. No strong magnetic field or field gradient is needed. We believe that the p-FMMD technique will become an alternative method in the field of MPI. Potential application areas include the analysis of biological tissue sections for diagnostic purposes. With a re-design to accommodate thicker samples, non-invasive studies of larger objects and small animals will become feasible.

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The authors have nothing to disclose.


This work was supported by the ICT R&D program of MSIP/IITP, Republic of Korea (Grant No: B0132-15-1001, Development of Next Imaging System).


Name Company Catalog Number Comments
Magnetic particles "SiMAG Silanol" Chemicell ( 1101-5 Aqueous dispersion of magnetic silica particles, Maghemite, dia. 1 µm
Magnetic nanoparticles "fluidMAG-Amine" Chemicell ( 4121-5 Aqueous dispersion of magnetic nanoparticles, Magnetite, dia. 50 nm
Microtube 10 µl Hirschmann Laborgeräte ( volume 10 µl, outer diameter 400 µm, length 40 mm
Nitrocellulose Membrane Biodyne B Thermo Scientific ( 77016 Biodyne B Nylon Membrane, 0.45 µm, 8 cm x 12 cm
DDS chip AD9834 Analog Devices ( AD9834 20 mW Power, 2.3 V to 5.5 V, 75 MHz Complete DDS
Operational Amplifier AD829 Analog Devices ( AD829 High Speed, Low Noise Video Op Amp
Analog Multiplier MPY634 Texas Instruments ( MPY634 Wide Bandwidth Precision Analog Multiplier
High-Speed Buffer BUF634 Texas Instruments ( BUF634 250 mA High-Speed Buffer
Operational Amplifier OPA627 Texas Instruments ( OPA627 Precision High-Speed Difet(R) Operational Amplifiers
Operational Amplifier TL072 Texas Instruments ( TL072 Dual Low-Noise JFET-Input General-Purpose Operational Amplifier
Lock-In Amplifier SR830 Stanford Instruments ( SR830 100 kHz DSP lock-in amplifier
XYZ motorized stage Sciencetown, Incheon, Korea (
Cleanroom wiper Seoul Semitech Co ( CF-909 dimension 2.0 mm × 18 mm



  1. Tseng, P., Judy, J. W., Di Carlo, D. Magnetic nanoparticle-mediated massively parallel mechanical modulation of single-cell behavior. Nat meth. 9, (11), 1113-1119 (2012).
  2. Borgert, J., et al. Fundamentals and applications of magnetic particle imaging. J. Cardiovasc. Comput. Tomogr. 6, (3), 149-153 (2012).
  3. Buzug, T. M., et al. Magnetic particle imaging: introduction to imaging and hardware realization. Z. Med. Phys. 22, (4), 323-334 (2012).
  4. Kanger, J. S., Subramaniam, V., van Driel, R. Intracellular manipulation of chromatin using magnetic nanoparticles. Chromosome Res. 16, (3), 511-522 (2008).
  5. Magnetic Nanoparticles: From Fabrication to Clinical Applications. Thanh, N. T. K. CRC press. Boca Raton. ISBN: 978=1439869321 (2012).
  6. Saritas, E. U., et al. Magnetic Particle Imaging (MPI) for NMR and MRI researchers. J. Magn. Reson. 229, (4), 116-126 (2012).
  7. Goodwill, P. W., et al. X-space MPI: magnetic nanoparticles for safe medical imaging. Adv. Mater. 24, (28), 3870-3877 (2012).
  8. Yim, H., Seo, S., Na, K. MRI Contrast Agent-Based Multifunctional Materials: Diagnosis and Therapy. J Nanomat. 2011, (2011), (2011).
  9. Gleich, B., Weizenecker, J. Tomographic imaging using the nonlinear response of magnetic particles. Nature. 435, (7046), 1214-1217 (2005).
  10. Rahmer, J., Weizenecker, J., Gleich, B., Borgert, J. Analysis of a 3-D system function measured for magnetic particle imaging. IEEE Trans. Med. Imaging. 31, (6), 1289-1299 (2012).
  11. Goodwill, P. W., Conolly, S. M. Multidimensional x-space magnetic particle imaging. IEEE Trans. Med. Imaging. 30, (9), 1581-1590 (2011).
  12. Goodwill, P. W., Konkle, J. J., Zheng, B., Saritas, E. U., Conolly, S. M. Projection x-space magnetic particle imaging. IEEE Trans. Med. Imaging. 31, (5), 1076-1085 (2012).
  13. Gräfe, K., et al. An Application Scenario for Single-Sided Magnetic Particle Imaging. Biomed. Tech. 57, Suppl. 1 (2012).
  14. Krause, H. -J., et al. Magnetic particle detection by frequency mixing for immunoassay applications. J. Magn. Magn. Mater. 311, (1), 436-444 (2007).
  15. Meyer, M. H. F., et al. Francisella tularensis detection using magnetic labels and a magnetic biosensor based on frequency mixing. J. Magn. Magn. Mater. 311, (1), 259-263 (2007).
  16. Finas, D., et al. Detection and distribution of superparamagnetic nanoparticles in lymphatic tissue in a breast cancer model for magnetic particle imaging. Biomed. Tech. 57, Suppl. 1 (2012).
  17. Hong, H., Lim, J., Choi, C. -J., Shin, S. -W., Krause, H. -J. Magnetic particle imaging with a planar frequency mixing magnetic detection scanner. Rev. Sci. Instr. 85, (1), 013705 (2014).
  18. Haegele, J., et al. Toward cardiovascular interventions guided by magnetic particle imaging: First instrument characterization. Magn. Reson. Med. 69, (6), 1761-1767 (2012).
  19. Haegele, J., et al. Magnetic particle imaging: visualization of instruments for cardiovascular intervention. Radiology. 265, (3), 933-938 (2012).
  20. Goodwill, P. W., Lu, K., Zheng, B., Conolly, S. M. An x-space magnetic particle imaging scanner. Rev. Sci. Instrum. 83, (3), 033708 (2012).
  21. Lampe, J., et al. Fast reconstruction in magnetic particle imaging. Phys. Med. Biol. 57, (4), 1113-1134 (2012).
  22. Yim, H., Seo, S., Na, K. MRI Contrast Agent-Based Multifunctional Materials: Diagnosis and Therapy. J Nanomat. 2011, (2011), (2011).



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