Research Article
Journal of Medical Research and Health Sciences
ISSN: (Print) 2589-9023 | (Online) 2589-9031
www.http://jmrhs.info
Received: 1 July 2019 Accepted: 15 July 2019
Change in Population of Hydrogen Proton Magnetic Dipole Moment at
Relaxation in the Blood as a Basis for Blood Pressure Monitoring
1
B.M.E. Jati , 2A.B.S. Utomo, 3G. Maruto, 4Y.R. Utomo
1,2,3,4
Physics Department, Universitas Gadjah Mada, Yogyakarta, Indonesia
Abstract: The research has been carried out to create a non-invasive blood pressure monitoring system in the branchial artery of a sample based on a rotating of the magnetic spin dipole moments of proton in hydrogen atom. This is motivated by the fact that change the population of a sudden and relaxation of the magnetic spin dipole moment of a proton in the hydrogen atom shortly after passing through the gap between magnetic poles (the strength of 1,200 gauss) can produce an induced emf. The system utilizes two permanent magnets and the receiver coil, and the system is called a magnet coil system. In this research, the writer wants to produce a non-invasive monitor for blood pressure but based on pulses of blood pressure waves. This study aims to get the value of equality between electromotive force induction which is washed away with blood (in the branchial artery) to the value of blood pressure from a number of samples measured by a sphygmomanometer. In addition, the total reproducibility of the tool is also calculated. As for the methodology carried out is to place the sample arm between the two permanent magnetic poles with a magnitude of (7.3 0.2)x103 gauss, and the electromotive induction is captured by receiver coil (involving 2,000 turns and 0.1 mm wire diameter). The receiver coil is connected with a digital storage oscilloscope. The result of equality between electromotive force induction (by rotation of the magnetic spin dipole moments of a proton in hydrogen atom at the time of relaxation) is obtained by the number of the digital sphygmomanometer from about 50 arms sample in the region of the induced electromotive force value of 0 to 80 mV and sphygmomanometer of 0 to 220 mmHg. The induced emf value is 4 times greater than when using a permanent magnet whose magnetic field is only about 1,200 gausses. While the total reproducibility of the magnet coil system is (20 1).
Keywords - magnet coil system, blood pressure, change in population
Introduction
The blood pressure monitor is a tool to monitor health in someone which is popular today [1,2]. Blood pressure referred to is blood pressure in the systematic blood circulation. Selected systematic blood circulation (heart – whole body – heart) and not pulmonary blood circulation (heart – lungs – heart) because in the systematic blood circulation passes through a number of vital organs (heart, kidney, and brain) and also in that circulation monitoring can indirectly (non-invasive) [3,4,5]. Besides that, in the systematic blood circulation, blood pressure monitoring in the sample is usually carried out in the sample arm because the location is close to the heart so that the results of the monitoring are more sensitive to the variation of blood pressure by contraction and relaxation in the heart. Other benefits, monitoring can be done
Figure-1 The tool monitors blood pressure in an: indirect (a,b,c) and direct manner (d)
At this time, a blood pressure monitoring device is needed with a new technique (the third technique) which is based on the superiority of blood pressure monitoring devices by the first technique and the second technique. The third technique of blood pressure monitoring has advantages: safe (non-invasive) and practical (like SPY), but monitoring can be carried out continuously without interfering with the flow of blood in the artery (like a catheter). This blood pressure monitoring tool can be used for healthy people or sick people [10,11, 12, 13]. The blood pressure monitor device is related to the principle of nuclear magnetic resonance (NMR) by change the population of sudden and relaxation (CPSR) of the magnetic spin dipole moments of a proton in the hydrogen atom (MSDMPHA). As for information on the value of blood pressure, both systolic pressure (SP) and diastolic pressure (DP) based on electromotive force (emf) value of induction by CPSR of MSDMPHA at the interval of transverse relaxation time ( ). Monitoring is carried out on the branchial artery (non-invasively), at that location (the SP value is different with DP value) sharper because the distance of the artery to the heart is close [14, 15, 16, 17].
On the same material (i.e. blood) the induced emf in a sample depends on the population of MSDMPHA and the value of pressure (drift speed) of the blood in the artery. While the population can be optimized by giving greater magnetic field strength by a permanent magnet. The value of blood pressure in the arteries is related to the cardiac activity (contraction and relaxation) and it is closely related to the condition of the sample.
II.Material and Experimental Method
This study involved research material (sample arms) and a number of equipment. The research material consisted of about 50 sample arms, each arm
containing two data points (corresponding to SP and DP) so that a total of about 100 sample points were obtained. Each of these data points is sought for equality between induced emf (in volts) and blood pressure (in mmHg). In addition, a trial involving 10 sample arms was also carried out, measured by 3 gauges to get the total reproducibility value. While the equipment used in this research is divided into two, namely factory product equipment and homemade equipment. Factory product equipment is both digital and aneroid SPY. Aneroid SPY acts as a digital SPY calibrator. In addition, digital storage oscilloscope also needed. Meanwhile, homemade equipment includes permanent magnet systems, filter-amplifier, and receiving coils (RC). Magnetic system remain useful for making minimum potential energy of MSDMPHA (in the blood at branchial artery) when MSDMPHA position is between the two magnetic poles. As for RC it is used to capture changes in magnetic field flux by CPSR of MSDMPHA so that the emf induction is founded. Filter-amplifier is used to amplify the 500 times indeed emf signal and filter signals so that only low-frequency signals (less than 20 Hz) can pass to be displayed on the oscilloscope screen.
This research involves two activities, namely planning and making tools, and testing. The plan for making a permanent magnet system is done by the author, while the making of the tool is done by the workshop. Hence, this experimental method also describes planning and experimental steps to obtain results according to the purpose of this study. The permanent magnet system that has been made is intended to produce a strong magnetic field of (7.3 0.2)x103 gauss. It is expected that the magnitude of the magnetic field will increase the optimal population of minimally potential energy ( ). While the gap between the north (N) and the south (S) pole on the permanent magnet can be adjusted, so that the tool can be used for a variety of sample diameter arms. The design of the permanent magnet system (Figure-2) is adjusted to the comfort of the sample when it is being tested.
RC is made in (7x7) cm2 dimensions, involving 2,000 turns of wire, and wire used in 0.1 mm diameter. The coil is useful for capturing changes in the magnetic field flux by the rotation of the MSDMPHA so that it produces induced emf. This dimension is chosen because to get about 70% of the MSDMPHA transition requires time around the time of relaxation. On the case, for blood is 0.2 s and the rate of mean blood flow (inside the branchial artery) is around 0.5 m/s. Hence, to reach the interval of , an effective arterial length of 10 cm is needed so that the RC length is 7 cm because the distance of the permanent magnet is the closest end of RC is 3 cm. Because of blood is 0.2 s so that the induced emf frequency produced is less than 20 Hz. It means that this system is insensitive to the presence of skin resistance. Therefore, a small diameter of the wire (0.1 mm) is chosen with the intention that the number of wire windings in RC is maximal (2,000 turns). The number of turns is intended so that the resulting induction emf is also maximal.
The experimental method is done by placing the sample arm between the two permanent magnetic poles, while the sample hand is inside the RC. The induced emf (by CPSR of MSDMPHA) obtained from this coil is connected to a filter-amplifier. The output of the filter-amplifier is connected to a digital storage oscilloscope to display the signal on the screen. The signal represents SP for large voltage and DP for small voltage. The test was conducted on about 50 sample arms (Figure-3) and reproducibility tests based on the analysis of variance (ANOVA) method.
Figure-3 Chart setup tools for experiment Iii. Experimental Result
From this research, permanent magnet and RC system have been obtained (Figure-4). Next, the permanent magnet and RC system are integrated with filter-amplifier and oscilloscope called magnetic coil system (MCS). MCS was tested on about 50 sample arms (Figure-5). Each sample
monitored for BP with the MCS was compared with the results of monitoring using SPY. Furthermore, in each arm of the sample, the equality between the induced emf value of MCS (in mV) and the reading value by SPY (in mmHg) is shown in Figure-6.
Figure-4 Portrait of the permanent magnet system (a,c,d) and RC (b) that have been made
Figure-5 (a) Portrait of one sample while being tested, (b) the signal pattern displayed
Furthermore, from the setup of the tool, it can also be searched for the total reproducibility value based on the ANOVA method [18, 19]. In this method, the test is carried out on 10 sample arms, measured by 3 gauges, and each sample is measured by each gauge twice. Measured data to obtain the total reproducibility value is shown in TABLE 1. The calculating of the total reproducibility based on TABLE 1 which is separated into 2, namely the systolic and diastolic parts. Next, consistent with the ANOVA method for 30 test data, the total reproducibility value for systolic was 19.6 while diastolic gave 20.7. The result of the combination of the two total reproducibility values gives a total reproducibility value of MCS of ( ) or around 70%. This value is equivalent to the reproducibility of digital SPY which is commonly used for blood pressure measurement services.
TABLE-1 Blood pressure data on the total reproducibility test by MCS
IV. Discussion
Based on the results of the experiments above (Figure-6), this can be explained based on Figure-7. The figure shows blood flowing direction (in the branchial artery) from left to right. Originally (at the far left) MSDMPHA or ⃗ (in the blood) was randomly directed. When ⃗ is in the gap between the two magnetic poles (N and S) which gives a ⃗⃗ magnetic field then ⃗ is oriented parallel ⃗⃗ so the potential energy ( ⃗ ⃗⃗) is minimum. Selected
⃗⃗ has a large value with the ⃗ of the population with minimum potential energy ( ) is a maximum
number. After passing through the gap between the two magnetic poles, the direction ⃗ is oriented randomly again.
Figure-7 The experimental setup chart along with the form of analysis,
With fluctuating No related to systolic and diastolic
The CPSR of MSDMPHA happens along the RC, and MSDMPHA population (at is ) then the population decreases up to 65% when the MSDMPHA is at a distance ( cm) from . It occurs because the speed of blood flow in the brachyal artery is around 0,5 m/s and the time interval corresponds to the time of transverse relaxation ( = 0,2s). Reduced population is caused by the CPSR of MSDMPHA causes the emergence of magnetic field flux ( ). When ⃗ moves through distance from the end of permanent magnetic poles, the minimum potential energy of ⃗ population changes to . Hence, the rate of changes in in the region to is proportional to the difference to and also the rate of change ( ). The magnitude of and are proportional to the emf induction received by RC.
As for the population of minimum energy of ⃗ at
is
(1) When the population of ⃗ changes from (at
) to (at ) because it shifts after then the induced emf is generated
(2) In the meantime, emf induction by the rate of change
is equal to
That is, the induced emf generated by population changes ⃗ of the minimum potential energy on the trip along at the time (transverse relaxation time) is
∫ ( ) ( ) (4)
Equation (2), (3), and (4) show that the induced emf value is an affected by the value of and also . In this research, is chosen to have a fixed value (10 cm) and that value is related to the optimal change in population (from its minimum potential energy). Hence, changes in are caused by changes in that occur in each by a blood flow that is not steady. Due is proportional to the rate of the CPSR of MSDMPHA entering the RC and also the density of MSDMPHA so that in accordance with the law of Continuity, is not only proportional to and but also proportional to the flow rate of blood in the branchial artery ( ). In the range m/s, then equation (4) is consistent with Figure-6. While the total reproducibility (systolic-diastolic) produces 70%. That is, the value is able to establish hope that output of this research can be used for service as a tool to monitor blood pressure.
V. Conclusion
Based on the results of the experiments above and that analysis it can be concluded that the CPSR of MSDMPHA in the blood can produce an emf induction and the value of the emf induction is proportional to the value of the blood pressure. In addition, the larger magnetic field strength can produce a larger rotational population which is also greater so that the resulting induced emf is greater, which is equal to 40 volts in a strong magnetic field of about 7,300 gausses whereas it is only 18 mV in 2,000 gausses [20]. Based on the equality between the emf induction by MCS and the sample blood pressure value by SPY, it can be concluded that this technique can be used as a tool for monitoring blood pressure by the technique-3. As for the total reproducibility of this homemade MCS is 70%.
Acknowledgment
On this occasion, the author expressed his gratitude to Mr. Suryono (UNDIP, by the help of an electric current rectifier system), Mr. Kuwat Triyana (UGM, giving permanent magnets), Mr. Suparwata (UGM, making filter-amplifiers), and Mr. R. Sumiharto (UGM, lending digital storage oscilloscope). Also, say thank you to Mr. Jamhari (UGM) on services workshop in order to make the device permanent magnet be comfortably used by the user. Also expressed gratitude for the help of tools and
ingredients to the laboratory of Basic Physics, Fisanti, Fismatel, and also Geophysics. And also, in particular, thank you very much to Mr. Djoko Untoro (Sanata Dharma University) for operational guidance on storing experiment data.
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