1
Faculty of science and technology
Defining the resolving power and detection depth of the DiffMag
handheld probe
Bas Bloemendaal B.Sc. Thesis
July 2020
Supervisors:
dr. ir. L. Alic E.R. Nieuwenhuis M.Sc.
dr. E. Groot Jebbink
Magnetic Detection and Imaging group
Faculty of science and technology
University of Twente
P.O. Box 217
7500 AE Enschede
The Netherlands
Samenvatting
Momenteel wordt in meerdere zorgcentra de schildwachtklier (SKW) biopsie (SKWB) procedure gebruikt voor het diagnosticereen van de lymfeklierstatus bij hoofd-hals kanker. De SKW’s zijn de lymfeklieren die de grootste kans hebben op een uitza- aiing afkomstig van de primaire tumor. Daarom spelen deze SKW’s een cruciale rol in het maken een prognose. De SKWB procedure bestaat uit het opsporen, operatief verwijderen en het diagnosticeren van een eventuele tumoruitzaaiing naar de SKW’s. Na verwijdering van de SKW wordt deze naar de pathologie gebracht om uiteindelijk een prognose over de kanker te geven. Momenteel wordt de SKW opgespoord met behulp van radio-actieve tracers en een gamma probe of met behulp van blauwkleuring. Echter, deze opsporingsmethoden brengen logistieke problemen en veiligheidsproblemen door de radio-actieve tracer en verstoring van het operatie veld van de chirurg door de blauwkleuring. Tevens, radio-active tracers brengen een
”shine-through” fenomeen mee, waardoor het signaal dat gemeten wordt met een gamma probe minder accuraat is in het detecteren van SKW’s. Om deze bijkomende nadelen te overkomen wordt er een nieuwe methode met magnetische detectie on- twikkeld.
Deze nieuwe magnetische detectie methode is vergelijkbaar met de radio-actieve methode alleen bestaat de magnetische tracer uit superparamagnetische ijzeroxide- nanodeeltjes (SPIONs). Deze deeltjes wordern peritumoraal ingespoten en vervol- gens opgespoord met een magnetische handheld probe in de omliggende schildwachtk- lieren. De magnetische detectie handheld probe exploiteert de niet-lineaire eigen- schappen van de ingespoten SPIONs om deze op te sporen in een diamagnetische (lineaire-) omgeving. Dit concept wordt differenti¨ ele magnetometry (DiffMag) ge- noemd. Deze DiffMag handheld probe bestaat uit een excitatie-en detectiespoel. De excitatiespoel exciteert een magnetisch AC-excitatieveld dat gemoduleerd is met een pulssequentie. Deze pulssequentie geeft het exciatieveld een offset mee die ervoor zorgt dat alleen de response van de SPIONs gemoduleerd wordt waardoor diamag- netische deeltjes niet gemeten worden. De response van de deeltjes wordt vervolgens door de detectiespoel gemeten. Hierdoor is een selectieve methode voor het deterc- teren van SPIONs mogelijk.
Voordat deze DiffMag handheld probe voor klinische doeleinden kan worden ge-
bruikt, moet deze aan een aantal klinische voorwaarden voldoen. De meest be-
langrijke voorwaarden zijn het onderscheidend vermogen en de maximale detectie
diepte. Om deze voorwaarden te evalueren voor de DiffMag handheld probe is een
MATLAB
®simulatiescript van de probe ontworpen. Voor het maken van deze sim-
ulatie is rekening gehouden met de exacte technische specificaties van de gegeven
CHAPTER 0. SAMENVATTING
Eerst is er een simulatie genaakt van het gecre¨ eerde exciatie en detectieveld. Vervol- gens is de respons van de SPIONs op dit exitatiesignaal gesimuleerd. Deze respons is berekend voor verschillende dieptes en laterale afstanden. Met deze respons is vervolgens een verband opgesteld tussen de detectie diepte en het onderscheidend vermogen.
Het model is gevalideerd aan de hand van metingen. Deze metingen zijn vericht aan een sample met MagTrace. De resultaten van de metingen waren niet afdoende om het model te valideren.
De detectie diepte van de DiffMag handeheld probe voldoet niet aan de de klinsiche voorwaarden voor het detecteren van SKW’s. Daarentegen is het oplossend vermo- gen van de DiffMag handheld probe op een maximale axiale afstand van 1.06 cm hoog genoeg om het ”shine-through” fenomeen te overkomen.
iii
Contents
Samenvatting ii
1 Introduction 1
1.1 Shine through phenomenon . . . . 3
1.2 Concept of Differential Magnetometry . . . . 4
1.3 Scope of this thesis . . . . 6
2 Methods 7 2.1 Specifications and Requirements . . . . 7
2.2 Model of DiffMag handheld probe . . . . 9
2.2.1 Simulating the DiffMag signal in MATLAB
®. . . . 9
2.2.2 Simulating the detection depth and resolving power of the handheld probe in MATLAB
®. . . 10
2.3 Validation . . . 12
2.3.1 Detection depth . . . 12
2.3.2 Resolving power . . . 14
3 Results 15 3.1 Simulation results . . . 15
3.2 Validation results . . . 22
4 Discussion 24 5 Conclusion 26 6 Recommendations 27 Appendices References 29 A Appendix A 32 A.1 Experimental validation . . . 32
A.2 List of symbols, units, elementary constants and quantities . . . 33
A.3 MATLAB
®script usage . . . 34
A.4 SPIONs’ response
for different currents . . . 35
Chapter 1
Introduction
On annual basis head and neck cancer (HNC) accounts for 500.000 registered cases worldwide and for 3000 cases in the Netherlands [1, 2, 3]. HNC is the 8th most common tumour for men and the 9th for women [4]. Lymphatic neck metastasis is the most crucial in prognosis and thus of high importance in treatment decision making[5]. The sentinel lymph nodes (SLN) are lymph nodes which have the high- est odds of being drained by a tumour in the head and neck region. [5]. Head and neck carcinoma are often squamous cell carcinomas and contain the pharynx, larynx, paranasal sinuses, nasal cavity, the salivary glands and the oral cavity which consists of i.e. the tongue and the floor of the mouth (FOM) [6]. A sentinel lymph node biopsy (SLNB) is performed for selectively SLN staging. The SLN is removed for histopathological examination to determine the lymph node status. The SLNB procedure is proven for breast cancer while it is viable for head and neck cancer but not commonly utilized yet [7].
The current standard of care of the SLNB is to utilize a radioactive tracer(Technetium- 99
mor
99mTc nanocoll) or blue dye that is injected near to the primary tumour. Blue dye is used for visual guidance while the radioactive tracer is detected with a gamma handheld probe. Afterwards the gamma probe is used to find the SLN. Finally, the SLN which contributes most to the measured signal, is removed. A new measure- ment will be performed after removing the SLN in order to inspect if there is still a signal coming from the region of interest or not. For metastatic identification, the dissected SLN(s) are examined by histological protocol [8]. However, the use of radioactive tracers for the SLNB procedure is not ideally as there are issues with safety and logistics as well [9, 10]. Further, blue dye has several drawbacks as well like concealing the intraoperative field of view of the surgeon and leaving a tattoo strain on the skin [10].
Therefore, a new option for SLNB could be magnetic detection with Super Para- magnetic Iron Oxides (SPIONs). This magnetic detection will have advantages compared to the current standard of care of a SLNB procedure. The magnetic de- tection of SPIONs with SentiMag
®(Endomagnetics ltd., London, United Kingdom) is already proven feasible for breast cancer and not inferior to the current standard of the SLNB procedure [10]. Nevertheless, this technique depends on the linear magnetic response of the SPIONs and is thus exposed to signal coming from dia- magnetic tissue [11]. To improve the magnetic detection of SPIONs in the SLNB procedure, Differential Magnetization (DiffMag) is currently being researched. This technique exploits the non-linear magnetic characteristics of the SPIONs which can improve the selectivity and sensitivity of intra-oprative magnetic detection for the
1
CHAPTER 1. INTRODUCTION
SLNB procedure[11]. The difference between the linear and non-linear magnetiza- tion curve is shown in Figure 1.1.
Figure 1.1: Difference between the magnetization for an ideal SPIO nanoparti-
cle(blue) and diamagnetic(red) matter against the same applied magnetic field [11].
CHAPTER 1. INTRODUCTION 1.1. SHINE THROUGH PHENOMENON
1.1 Shine through phenomenon
Detection of carcinomas situated in the FOM is far more difficult than carcinomas in other sites of the oral cavity [12, 13, 14]. This is due to the shine-through phe- nomenon that causes an inability to differentiate between the signals from SLNs and the primary tumour[12]. This phenomenon is caused by the proximity between the peri-tumoural injection site and the SLNs along with the insufficient resolving power of the current detection techniques as the SentiMag
®and gamma probe [12, 14].
The gamma probe has a linear relationship between the resolving power and axial distance [15]. This means that the resolving power becomes worse as the measure- ments are further from the gamma probe. The resolving power is defined as the closest distance at which two point sources can be distinguished. The proximity between the injection site and SLN can be as close as 13 mm [16, 17]. This shine- through phenomenon causes the SLNB to fail. This phenomenon can be illustrated in Figure 1.2.
Figure 1.2: Visual representation of the shine-through phenomenon. T represents the primary tumour whereas the red circle represents a SLN in the close vicinity of the tumour. The yellow circle reflects the focus of the injection site. The yellow circle overshadows the SLN and primary tumour which causes the shine-through phenomenon. As a result, the SLN can not be identified. Figure from [12].
3
1.2. CONCEPT OF DIFFERENTIAL
MAGNETOMETRY CHAPTER 1. INTRODUCTION
1.2 Concept of Differential Magnetometry
A refinement of the SentiMag
®could be the DiffMag handheld probe. Both mag- netometers exists of an excitation and detection coil. The magnetometer excites a magnetic field by putting a current through an alternating current (AC) coil and de- tects signals with a detection coil. The DiffMag handheld probe is a magnetometer with an additional DiffMag procedure [9]. The DiffMag handheld probe technique exploits the non-linear SPION’s behaviour. Because of the different physical be- haviour between the SPIONs and human diamganetic tissue, the response to an applied external magnetic field will be different as perceived in Figure 1.3.
Figure 1.3: Concept of DiffMag. The colors red, blue and green correspond to the offset field -20, 0, +20 respectively. To the left: different response to an applied alternating field. To the right: (C) gives the different magnetization of the SPIONs.
The red and green colors are corresponding to the small amplitude to the lower right graph. (D) represents the time derivative of the magnetization (∆U ), which is equal to the difference between DiffMag signal amplitude with zero offset and non-zero offset. Figure acquired from [18].
An AC modulated field with and without direct current (DC) or offset results in
different signal amplitudes for SPIONs [19]. DiffMag is able to detect this difference
and thus DiffMag can detect the SPIONs in a diamagnetic environment. As pre-
sented in Figure 1.3, the amplitude of the signal is higher with zero DC offset than
with non-zero offset. The DiffMag signal amplitude is now obtained by subtraction
of the signal without DC offset minus the signal with DC offset. Now, the SPIONs
show a high signal compared to the approximate zero signal of the diamagnetic
tissue.
CHAPTER 1. INTRODUCTION
1.2. CONCEPT OF DIFFERENTIAL MAGNETOMETRY
The excitation coil of the DiffMag handheld probe generates a magnetic field that can be described with Equation 1.1 [9]:
H = H
ACsin(ωt) + H
DC(1.1)
The SPIONs’ response is measured in the detection coil of the DiffMag handheld probe according to Faraday’s law of induction[18]. The response of the SPIONs to the applied magnetic field can be approximated by the Langevin Equation:[11, 19, 18]:
M = M
sL(x), with L(x) = coth(x) − 1/x (1.2) Here, M
sis the saturation magnetisation in A/m. Due to the magnetic susceptibility of the SPIONs, the magnetization of the SPIONs will change with the frequency of the excitation signal and will induce a voltage in the detection coil which is proportional to the time derivative of the SPION-specific magnetization [18, 11]:
U = −ωS(z)V
cM = dM
dt (1.3)
Here, ω = 2πf in rad/s, S(z) in the coil constant in T/A and V
cthe core volume
that contains the iron oxide in m
3.
1.3. SCOPE OF THIS THESIS CHAPTER 1. INTRODUCTION
1.3 Scope of this thesis
The main clinical application that is focused on is a SLNB, which is intended to resect lymph nodes with highest chance on containing potential metastases. The current standard of care for a SLNB has several drawbacks. A magnetic procedure to perform the SLNB will have advantages like less complex logistics and safety risks.
This new method utilizes SPIONs. These nanoparticles are usually injected peri- tumoural and accumulate in a primary tumour and in (regional) SLNs. Although this magnetic SLNB procedure is proven viable, some false-positive cases could arise due to the shine-through phenomenon as this is the case with the gamma probe.
Ongoing research involves development of detection methods for both open and la-
paroscopic surgery. Some technical specifications must be defined for the differential
Magnetometry (DiffMag) handheld probe, before the probe can be utilized in the
clinic. Hence, the following question: ”What is the resolving power and detection
depth of the simulated DiffMag handheld probe?”. Therefore, the scope of this re-
search is to simulate the detection depth and resolving power with regard to the
DiffMag handheld probe.
Chapter 2
Methods
A list of clinical requirements is assembled for the DiffMag handheld probe. The detection depth and the resolving power are the most important requirements for clinical employment. First a list of specifications of existing methods is being assem- bled. The list of specifications will be based on the gamma probe and the SentiMag
®specifications whereas the list of requirements will be based on the clinical SLNB requirements. An important specification of the handheld probe must be a high resolving power which means a small FWHM is required [11, 20].
2.1 Specifications and Requirements
In order to perform a SLNB in the head and neck area, a localization of the SLN is required. The detection depth is defined as the deepest point in space where SPIONs can be detected. The cervical lymph nodes are rooted 3 ± 1.1 cm deep in the neck [21]. Therefore a maximum depth for transcutaneus detection would be 4.1 cm whereas the minimum depth will be 1.9 cm. The resolving power is defined as the shortest distance between two sources in which these sources can be detected independently. A high resolving power is required to detect a SLN close to the injection site in the neck area [16]. Table 2.1 summarizes the experimentally established detection depth and resolving power for the DiffMag handheld probe, SentiMag
®and the gamma handheld probe. The in vivo detection depth of the SentiMag
®is 2.5 cm for an uptake of 500 µg of Sienna
+®, whereas this depth is 1.9 to 2.2 cm for an 50 µg uptake [22].
The detection depth of the DiffMag handheld probe is 1.0 cm for 4 µl of SPIONs[21].
Note that the uptake of SPIONs in a SLN is assumed to be the same as with
radioactive tracers. Therefore, the detection specifications are based on the same
volume of particles as for the gamma probe. In addition the detection depth of the
gamma probe can be very deep but loses its resolution quickly.
2.1. SPECIFICATIONS AND REQUIREMENTS CHAPTER 2. METHODS
The concentration and volume of iron oxides in the SLN is determinative for the detection depth and resolving power. For clinical applications in the head and neck area, a resolving power between 0.5 and 1.0 cm is required according to an head and neck oncologist from Medisch Spectrum Twente.
Table 2.1: Detection specifications.
Specification DiffMag (50 µL) SentiMag
®(50 µL) γ-probe
Detection depth [cm] 1.0 [21] 2.5 [22] 1.0≤ [16]
Resolving power [cm] (depth=0 cm) 1.9 [21] 2.4 [21] ≈3.5 [16]
CHAPTER 2. METHODS 2.2. MODEL OF DIFFMAG HANDHELD PROBE
2.2 Model of DiffMag handheld probe
The steps for developing the MATLAB
®(version 2018b, The MathWorks Inc., Nat- ick, MA, USA) script are run through. A model for simulating the detection depth and the resolving power is developed, with respect to the technical specifications of the DiffMag handheld probe. First, a DiffMag signal is produced alongside the simulation of the excitation and detection magnetic field (Bz). Second, a magnetic particle response will be added to the model. Last, a simulation of the detection depth along with its resolving power at that depth is made.
2.2.1 Simulating the DiffMag signal in MATLAB ®
First a schematic cross-section of the DiffMag handheld probe tip is illustrated in Figure 2.1. This DiffMag handheld probe contains an integrated system of the excitation and detection coils. The excitation coil produce a magnetic excitation field, called Bz
exin Tesla (T). The concern for the detection coils lie within the coil sensitivity in T/A. This coil sensitivity is a measure for the detection sensitivity and is called Bz in the MATLAB
®script.
Figure 2.1: Schematic cross-section of the tip of the DiffMag handheld probe with two detection and compensation coils (orange), two AC excitation coils (green) and one DC excitation coil (blue). Figure enquired from [9].
A set of global variables was created and gathered from [18]. By producing a mag- netic field with and without an offset, an excitation signal was produced according to Equations 2.1 and 2.2. Adding different offsets is possible to change the magne- tization of the SPIONs:
H(t)
up= V
cM s
K
bT (of f set + AC
amp) (2.1) H(t)
down= V
cM s
K
bT (of f set − AC
amp) (2.2)
Here V
cis the iron core volume of one particle in m
3, M
sthe saturation magnetization
in A/m, K
bthe Boltzmann constant and T the temperature which is set at the
temperature of the human body around 310 K. The offset is the DC signal which
later on can be simulated and is responsible for the early magnetic saturation of
the SPIONs compared to the diamagnetic tissue [18]. Also AC
ampis the amplitude
of the excitation signal that varies with the distance to the excitation coil. This
variation in signal strength over depth can be approximated by using the magnitude
of that magnetic field (Bz) at that exact same depth. This Bz field is induced
2.2. MODEL OF DIFFMAG HANDHELD PROBE CHAPTER 2. METHODS
by the excitation coil of the handheld probe and is simulated with the help of Soleno(in-house build, written in MATLAB
®, C++) according to Ampere’s law which describes the characteristics of the magnetic field originated from the changing electrical current[9].
The SPION magnetization can be calculated with the help of the Langevin equation.
The response of the SPIONs to excitation signal is equal to the time derivative of the magnetization:
d
dt M (t) = nM
sV
cf L(ξ
+) − L(ξ
−) (2.3) Here L(ξ
+) and L(ξ
−) are respectively the excitation fields with the highest and lowest offsets. These field parameters can be described with regard to Equations 2.1 and 2.2 and is given by:
L(ξ
+) = M
s(coth(H(t)
up) − 1
H(t)
up(2.4)
L(ξ
−) = M
s(coth(H(t)
down) − 1
H(t)
down(2.5)
Here, H is the dimensionless applied magnetic field. Substituting Equations 2.4 and 2.5 into 2.3 results in:
M
spions= nf V cM s(coth(ξ
up) − 1/(ξ
up) − coth(ξ
down) + 1/(ξ
down)) (2.6) with ’n’ the SPION density number in m
−3[19]. Equation 2.6 is written by Max Rietberg in MATLAB
®(version 2020a) and adjusted to fit into the model for simu- lating the SPION response. With the mentioned SPION’s magnetization response, the signal voltage (U
det, V) can now be calculated with the following Equation:
U
det/S
coil= − d
dt M (t) (2.7)
Here, S
coilis the coil sensitivity which varies over different depths. Plotting this against the offset, generates a signal that represents the response of the SPIONs.
2.2.2 Simulating the detection depth and resolving power of the handheld probe in MATLAB ®
In Section 2.2.1 a set-up was made to provide simulations. First an excitation signal was created followed by a response from the SPIONs to this signal. In this section the magnetic field produced by handheld probe is simulated in MATLAB
®with the Soleno function ’soleno calcB’. The input values can be found in Appendix 2.3.
The output values are 100x100 matrices containing the excitation magnetic field and the detection coil sensitivity for Bz
exand Bz respectively. These output values are given for axial distances lateral distances as described in Table 2.2.
First, an orientation for the axes can be perceived in Figure 2.2. The axial distance
represents the distance from the surface of the probe while the lateral distance
represents the distance to the axial axis.
CHAPTER 2. METHODS 2.2. MODEL OF DIFFMAG HANDHELD PROBE
Figure 2.2: Axes frame orientation with respect to a handheld probe.
Keeping this frame in mind, a 3D plot can be simulated with an induced magnetic field. This plot is constructed from magnetic field strength, produced by the DiffMag handheld probe and by a grid of lateral and axial distances from the handheld probe.
The specifications of the handheld probe are described in Table 2.3. According to Visscher et al., the background noise can be set to 10
−7V which is equal to 10 counts and is can be represented by a transverse (x,y = z) plane in the 3D representation.
Table 2.2: Grid of lateral and axial distances.
Axial distance in cm Lateral distance in cm Number of steps
0.1 to 4 -4 to +4 100
Table 2.3: Handheld probe specifications R
in[m] R
out[m] Z
low[m] Z
high[m] N
windings# 0.0060 0.0095 -0.0016 0.0000 380 0.0060 0.0095 -0.0196 -0.0180 -380
The Full Width Half Maximum (FWHM) of the SPIONs response is calculated for
each step in the depth (Z-) direction, in order to calculate the resolving power. This
is provided by taking the values of the detection signal amplitude for each depth at
each distance from the probe’s surface.
2.3. VALIDATION CHAPTER 2. METHODS
2.3 Validation
Two separate measurements are required to validate the MATLAB
®model as de- scribed in Section 2.2.1. Calibration is performed prior to each measurement. All measurements will be performed using the DiffMag handheld probe. The offset was changed to 30 mT only. Resolving power measurements are single measurements.
A sample with MagTrace SPIONs will be used for the measurements. Furthermore, all counts are written down in Excel
©(Microsoft, Washington, United States) after each measurement.
2.3.1 Detection depth
The measuring set-up, developed by Fleur van Wezel is utilized for the detection depth measurements. This set-up is illustrated in Figure 2.3. A volume of 50 µL pure MagTrace with a concentration of 28 µg/µL of iron nanoparticles is used.
The whole set-up for detection depth measurements is illustrated in Figure 2.4. The measurement with 50 µL sample is placed in the first hole (0 cm) and a measurement is run. The measurements are performed in duplo and shown in Figure 3.1. The measurement protocol for the axial distance is as follows:
1. Make a sample with 50 µL MagTrace with a concentration of 28 µg/µL.
2. Balancing DiffMag with a sensitivity of 100 nV.
3. Put the handheld probe in the standard.
4. Put the sample in the first hole of the foam measurement set-up.
5. Put the handheld probe in the foam measurement set up as well.
6. Start the measurement.
7. Write down the amount of counts into Excel.
CHAPTER 2. METHODS 2.3. VALIDATION
Figure 2.3: Set-up for detection depth measurements. The 1.6 cm holes are de- signed to pin the DiffMag handheld probe. the small holes in the bottom contain the samples. the holes are 0.0, 0.5, 0.7, 1.0, 1.3, 1.5, 1.7 and 2.0 cm far from the probe [21].
Figure 2.4: Complete measurement set-up for detection depth measurements.
2.3. VALIDATION CHAPTER 2. METHODS
2.3.2 Resolving power
Two tubes are filled with respectively 50 and 2.4 µL MagTrace. The tube with 50 µL represents the primary tumour whereas the 2.4 µL represents the SLN with a 4.8% uptake. This is percentage is based on the radioactive tracer uptake in the SLN which depends on the particle’s size[12, 22]. One measurement consists out of three parts:
1. Measurement with 50 µL.
2. Measurement exactly in between both samples (0.5*distance).
3. Measurement with 2.4 µL.
These three parts and the set-up are presented in Figure 2.5. These measurements are repeated for 10 different lateral distances. The distances are measured with a digital ruler.
Figure 2.5: Complete measurement set-up for lateral measurements. The numbers
in the probe represent the step that is described as above.
Chapter 3
Results
Visual representations of the calculations by the developed MATLAB
®script are shown. All results are based on the technical specifications of the DiffMag handheld probe. The simulation results will consist of representations of the excitation and detection field, the response of the SPIONs to this field and the final resolving power over different detection depths.
3.1 Simulation results
An induced magnetic excitation field in vacuum, responsible for the excitation of the SPIONs is produced. This excitation field is shown in Figure 3.1. The figure below is a simulation of the magnetic field over the axial and lateral direction. Note that this field begins at 0.1 cm instead of 0 cm because of the cover thickness of around 0.1 cm over the coils. The different colors of the field lines represent the strength of the magnetic field at that exact coordinate. The maximum field strength at the origin or center of the excitation coil is 6.15 mT while the minimum field strength is 0.23 mT at 2.39 cm axial distance.
-4 -3 -2 -1 0 1 2 3 4
lateral distance [cm]
0.5 1 1.5 2 2.5 3 3.5 4
axial distance [cm]
1 2 3 4 5 610-3
Figure 3.1: Produced magnetic excitation field by DiffMag handheld probe. The
different colors of the field lines represent the magnitude of the magnetic field in T.
3.1. SIMULATION RESULTS CHAPTER 3. RESULTS
In Figure 3.2, the produced magnetic detection field by the DiffMag handheld probe is simulated. What can be extracted from this plot is the strength or magnitude of Bz along the axial and lateral axis. Figure 3.2(a) represents how the magnetic field is behaving along the lateral axis. Figure 3.2(b) shows a smooth graph of the behavior of the magnetic field in the axial direction. Last, Figure 3.2(c) shows the magnetic field in all possible directions and has a maximum magnitude of Bz= 0.036 T at 0.1 cm depth.
(a) Bz superior view.
(b) Bz side view.
(c) Bz oblique view.
CHAPTER 3. RESULTS 3.1. SIMULATION RESULTS
Next, the simulation of the SPION response to the excitation signal with different offsets, is presented in Figure 3.3. The response of the SPIONs is decreasing due to an increasing offset.
Figure 3.3: Detected signal in counts 100 nV against an increasing offset in mT.
3.1. SIMULATION RESULTS CHAPTER 3. RESULTS
A representation of the SPION response to the magnetic field from Figure 3.2 can be perceived in Figure 3.4. The maximum amount of counts at 0.1 cm distance from the SPIONs is 40880 as can be perceived in Figure 3.4(b). The noise is simulated as a dark blue transverse plane with a magnitude of 10 counts. It is hard to see where the signal of the SPIONs stops and the SNR becomes too low. The response is plotted along the axial and lateral axis of the DiffMag handheld probe. The response of the SPIONs will be maximal when there is no distance between the probe and the SPIONs as can be seen in Figure 3.4. Also when the lateral distance increases, the signal amplitude in counts will decrease exponentially. What can be perceived in Figure 3.4(a) is a view of the behaviour of the received signal along the lateral axis. Figure 3.4(b) shows a smooth graph of the behavior of the magnetic field in the axial direction.
(a) SPION response top view. (b) SPION response side view.
(c) Zoomed in representation of (a). (d) Zoomed in representation of (b).
Figure 3.4: SPION response, top(a) and side(b) view with zoomed in representa-
tions.
CHAPTER 3. RESULTS 3.1. SIMULATION RESULTS
The maximum axial distance value can be found in Figure 3.5. The maximum distance is 1.06 cm as this is where the signal to noise ratio (SNR) becomes too low.
(a) Maximum axial distance where Bz ≥ noise.
(b) Maximum axial distance where Bz ≥ noise.
Figure 3.5: Maximum axial distance top view and side direction, where Bz ≥
noise. Color values expressed in T.
3.1. SIMULATION RESULTS CHAPTER 3. RESULTS
Nevertheless, it is still hard to exclude the direct relation between the resolving power and the detection depth. Therefore, the FWHM is calculated for each increase in axial distance and plotted along the axial axis as shown in Figure 3.6(b).
0 0.5 1 1.5 2 2.5 3 3.5 4
Axial [cm]
0.4 0.6 0.8 1 1.2 1.4 1.6 1.8
Lateral [cm]
(a) Lateral versus axial distance.
-4 -3 -2 -1 0 1 2 3 4
Lateral [cm]
0.1 0.15 0.2 0.25 0.3 0.35 0.4
Axial [cm]