The authors describe a compact non-invasive CMOS-circuit-based glucose monitor using millimeter-wave transmission for use on animal and human subjects. Using an earlier device, in vivo measurements were performed through the ear in anesthetized animals and correlated with blood glucose concentration from test strips. In addition, millimeter wave absorption through glucose-containing solutions was measured in specialized liquid transmission cells and is shown to correlate with the animal and separate in vitro data. Design and performance information on the CMOS transceiver are given

Chang, M. C. Frank

Kim, Yanghyo

Pikov, Victor

Siegel, Peter H.

Tang, Adrian

Virbila, Gabriel

Caltech Authors - Main

 
Abstract — The authors describe a compact non-invasive 
CMOS-circuit-based glucose monitor using millimeter-wave 
transmission for use on animal and human subjects. Using an 
earlier device, in vivo measurements were performed through the 
ear in anesthetized animals and correlated with blood glucose 
concentration from test strips.  In addition, millimeter wave ab-
sorption through glucose-containing solutions was measured in 
specialized liquid transmission cells and is shown to correlate 
with the animal and separate in vitro data. Design and perfor-
mance information on the CMOS transceiver are given. 
 
I. INTRODUCTION 
ONTINUOUS NON-INVASIVE monitoring of blood glu-
cose levels is a holy grail for researchers working on 
type 2 diabetes mellitus, estimated to affect almost 300 million 
people worldwide [1]. In 2014, two of the authors showed that 
millimeter-wave (MMW) transmission at a frequency between 
27 and 40 GHz (Ka band) can be directly correlated with abso-
lute readings of blood glucose levels in anesthetized rats [2]. 
MMW transmission through the ear reproducibly tracked 
changes in glucose levels (measured by blood glucose test 
strips) following injections of dextrose and insulin, and 
showed no change upon injections of saline (Fig. 1).  
The positive correlation between blood glucose levels and 
MMW transmission through the rat ear, coupled with signal 
changes that were well above the system noise floor when 
transmitter power is in the allowable safe exposure levels 
(1mW/cm2 for six minutes [3]), are very promising, but the 
rigid waveguide hardware used in the original experiments can 
only be employed on immobilized animals. The authors have 
now designed and fabricated a small light-weight clamp-on 
fixture containing a full MMW CMOS transceiver chip set and 
input/output antenna coupled to a tethered power/data transfer 
cable for active animal and human studies. Laboratory meas-
urements were also conducted on the transmission of MMWs 
through solutions of saline, and saline plus sugar, to see if they 
are consistent with both the in vivo rat ear measurements and 
in vitro measurements on blood made by other researchers. 
This paper discusses the in vitro and in vivo measurements, the 
CMOS transceiver design, and the design for a packaged non-
invasive glucose monitoring device. 
 
II. IN VITRO AND IN VIVO EXPERIMENTS 
We have shown [2] that low levels of transmitted MMW 
power through the ear of an anesthetized rat may be conven-
iently monitored and correlated with changes in the levels of 
blood glucose in vivo. The exact mechanism for these ob-
served changes in MMW absorption is as yet uncertain, but 
the effect is quite pronounced. In our in vivo measurements we 
observed a strong reduction in MMW power absorption 
through the rat ear with increasing glucose levels in the blood. 
This effect has also been observed in in vitro blood samples 
[4], [5]. In an attempt to quantify whether or not this change is 
due to a metabolic process (e.g. glycolysis) or to glucose con-
centration directly, we performed a series of laboratory ab-
sorption measurements for glucose and other fluids.  
Using a vector network analyzer (Anritsu 37397C) with our 
Ka band waveguide magnetically clamped around a sealed 
10ml fluid chamber (OptiCell, Thermo Fisher Scientific, 
Rochester, NY) [Fig. 2 insert], we recorded the transmitted 
power as a function of frequency for the following fluids: DI 
water, saline (0.9gm/dl) and saline plus glucose (1gm/dl). The 
results are shown in Fig. 2, where it is clear that adding glu-
cose to saline reduced the absorbed MMW power in the solu-
tion, just as in both the in vivo [2] and in vitro blood meas-
urements [4], [5] made by other researchers. Note that the data 
for glucose plus saline represents a concentration 10X a typi-
cal level in vivo and accounts for the much greater increase in 
transmission than what we observed in the rat studies (red vs 
blue in Fig. 2). We also were able to find a supporting article 
[6], which yielded similar results on saline plus glucose solu-
tions with concentrations comparable to those observed in 
vivo. Although not conclusive, these measurements strengthen 
the case for being able to directly measure glucose concentra-
tion, rather than some indirect glucose-triggered effect in vivo. 
Peter H. Siegel1, Adrian Tang2, Gabriel Virbila3, Yanghyo Kim3, M. C. Frank Chang4 and Victor Pikov5 
1California Institute of Technology and THz Global, Pasadena, CA, USA 
2UCLA and NASA Jet Propulsion Laboratory, Los Angeles, CA, USA 
3UCLA, Los Angeles, CA USA 
4UCLA and National Chiao Tung University, Hsinchu, Taiwan 
5Glaxo Smith Kline, Stevenage, UK 
Compact Non-Invasive Millimeter-Wave Glucose Sensor 
C 
Fig.1. Measured changes in MMW transmission through rat ear 
after injections of 1gm/kg glucose, 5ml saline (control) and 2U/kg 
insulin [2]. The power levels are extrapolated from the measured 
square law detector responsivity (approximately 0.28 mV/μW). 
III. CMOS CHIP SET 
The in vivo and in vitro measurements correlating glucose 
concentration increase to a reduction in MMW absorption, 
spurred us to design and fabricate a compact CMOS RFIC 
transceiver chip set that could be assembled into a wearable 
clip-on package, and used on awake and freely moving ani-
mals or humans. The chipset has the following functional ele-
ments: a tunable free running MMW oscillator, a power am-
plifier, a non-coherent pre-amplified receiver, and frequency 
and power control circuitry. DC power, detected signals, and 
all control functions on the RFIC are introduced via a 10 pin 
input/output connector and cable tethered to a control comput-
er USB port. Future RFIC generations will use wireless in-
put/output for control and data transfer. The chips were laid 
out and fabricated in a standard 65nm foundry process from 
TSMC, Taiwan and are shown in Fig. 3. 
 
 
 
 
 
 
 
 
 
 
 
 
 
 
 
 
 
 
 
 
 The transmitter is designed to generate up 3.1mW of tuna-
ble RF CW energy between 33 and 37 GHz. The receiver uses 
a non-coherent self-mixing detection circuit with an input re-
ferred detection limit of 1 nanowatt (-60 dBm). The expected 
loss through the tissue is between 20 and 30 dB, leaving plen-
ty of detection headroom even at 1mW/cm2 input power densi-
ty providing a final signal to noise (S/N) of 30-40 dB. When 
higher losses are encountered the gain can be increased sub-
stantially by reducing the transmitter duty cycle without ex-
ceeding any SAR safe limits in the tissue. Modulation is ap-
plied to the transceiver through a standard TTL input port. 
IV. PACKAGED TRANSCEIVER 
The transmit and receive chips are integrated onto the ends 
of separate printed circuit boards (PCB) composed of a 1.5mm 
thick RO4350B/bondply sandwich. Appropriate dielectric and 
metal ground plane regions are pre-etched into the PCB. Each 
RFIC must be coupled to an RF antenna that can radiate into 
the tissue (transmitting antenna) and pick up the power on the 
other side (receiving antenna). A small folded dipole was de-
signed and placed on the PCB close to the RFICs and coupled 
to the output/input port via short wire bonds (Fig. 4). 
  
The power, data and control tabs on each RFIC are wire 
bonded to pads that lead to a small 10 pin connector on the 
opposite end of the PCB. The antenna and RFICS are then 
coated with a BCB protection layer (Dow Chemical). Match-
ing to the tissue is accomplished by sanding the BCB layer 
down to a flat half-wavelength thick sheet and then adding 
(gluing) a quarter wavelength thick matching layer composed 
of low loss glass on top. A diagram of the antenna structure 
and EM simulation results using HFSS showing the predicted 
power transfer characteristics through 1mm of tissue are given 
in Figs. 5 and 6. 
The two PCBs are tied together in a clothes-pin type of ar-
rangement using rubber bands and a small cylinder as a pivot 
for the clamp (Fig. 7). Once in place the antennas are in inti-
mate contact with the tissue on both the transmitter and re-
ceiver sides, and continuous measurements can be performed 
on either animals or humans while the subjects are in an active 
state. The only inconvenience is the wire tether, which as stat-
ed earlier, will be replaced by a battery and wireless transceiv-
er system in the next generation circuitry.  
Fig. 2. RF transmission vs. frequency normalized to transmission 
without Opticell for DI water (green), saline (blue) and glucose plus 
saline (green). 1.0=no loss, 0.0=zero transmission. Incident power = 
1-1.3µW. Transmitted power = 0.05-0.1µW. Peaks and valleys are 
due to reflection off the Opticell.  
Fig.3. Die photographs of both the transmitter and receiver chips 
with overall dimensions in microns. 
 
Fig. 4.Antenna design for both transmitter and receiver. 
At time of writing the chips have been fabricated and deliv-
ered and the PCB holders have been sent out for processing. 
We expect to put the measurement clamp together and begin 
programming within the month. The first tests will be on 
awake rats with human trials to follow. 
 
V. SUMMARY 
After initial successful experiments tracking blood glucose 
levels via MMW transmission through the ears of anesthetized 
rats, and accurately correlating MMW absorption with sepa-
rate blood glucose test strips, the authors have been encour-
aged to extend their initial work. In this short paper they pre-
sent in vitro absorption measurements on solutions of saline 
and saline plus glucose, which correlate in direction and mag-
nitude with absorption changes measured in vivo. They also 
present a CMOS RFIC transceiver chipset operating between 
33 and 37 GHz that has the capacity to make high sensitivity 
coherent transmission or reflection measurements in CW or 
variable-duty-cycle pulsed operation. The transmitter and re-
ceiver modules have been coupled to a custom designed planar 
antenna that has been fabricated on a separate PCB board that 
also serves as a holder and clamping device for in vivo meas-
urements. The CMOS chips and antennas have been covered 
with a BCB protection layer that has been machined down to 
accept a matching layer that will help provide better power 
transfer into and out of the subject tissue. Designs and numeric 
simulations for the transceiver performance are presented.  
A simple clothes-pin style mount has been realized with a 
very flexible, but tethered input/output wired control system. 
Software for controlling the measurements and collecting the 
glucose data has yet to be developed. Since the instrumenta-
tion is designed to measure changing glucose levels, rather 
than absolute concentrations, we envision a continuously up-
dated, individually calibrated system for each user that can 
both establish a long term baseline for every activity level and 
warn of dramatic change without having to continuously cali-
brate against blood sampling. The clamp-on device will be 
tested on awake and active animals, and eventually configured 
for human trials. 
 
 
REFERENCES 
 
[1]. Lei Chen, Dianna J. Magliano, and Paul Z. Zimmet, “The worldwide 
epidemiology of type 2 diabetes mellitus—present and future perspectives,” 
Nature Reviews Endocrinology, vol. 8, pp. 228-36, 2012. 
[2]. P. H. Siegel, Y. Lee and V. Pikov, “Millimeter-wave non-invasive moni-
toring of glucose in anesthetized rats,” 39th Int. Conf. on Infrared, Millimeter, 
and THz Waves, paper T2_D8.10, Tucson, AZ, USA, Sept. 14-19th, 2014. 
[3]. IEEE Committee on Electromagnetic Safety (SCC39), “IEEE Standard 
for Safety Levels With Respect to Human Exposure to Radio Frequency Elec-
tromagnetic Fields, 3 kHz to 300 GHz,” Piscataway, NJ: IEEE, c. 2006. 
[4]. M. Hofmann, G. Fischer, R. Weigel and D. Kissinger, “Microwave-Based 
Noninvasive Concentration Measurements for Biomedical Applications,” 
IEEE Trans. MTT, v. 61, no. 5, 2195-2202, 2013. 
[5]. Tutku Karacolak, Elaine C. Moreland, and Erdem Topsakal, “Cole-Cole 
Model for Glucose Dependent Dielectric Properties of Blood Plasma for Con-
tinuous Glucose Monitoring,” Microwave and Optical Tech. Lett., v.55, no.5, 
116-64, 2013. 
[6]. Y. Nikawa and D. Someya. “Non-invasive measurement of blood sugar 
level by millimeter waves,” IEEE Int. Mic. Sym. Digest, pp. 171-4, 2001. 
Fig. 5. HFSS layout for transmitting and receiving antennas 
separated by 1mm of tissue (rat ear simulant). 
Fig. 6. Simulated (HFSS) transmitter matching (top) and power 
transfer function from transmit to receive antenna (bottom) for 
layout shown in Fig. 5. 
 
10	  pin	  connector 
Spring	  load-­‐ed Turnstile	  &	  clamp 
Interconnects 
Output	  wires 
Antenna Chip Tx Rx 
Fig. 7. .Layout for final clothes pin style clamp. 


Compact non-invasive millimeter-wave glucose sensor

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